Radiographic image capturing apparatus and method for supplying electric power thereto

ABSTRACT

A radiographic image capturing apparatus includes a mobile cart unit, a plurality of devices used for capturing a radiographic image, and an electric power supply activator enabling supply of electric power between the devices, based on an instruction of permission to supply electric power.

CROSS-REFERENCE TO RELATED APPLICATION

This application is a Continuation of U.S. patent application Ser. No.13/067,801, filed on Jun. 28, 2011, which is based upon and claims thebenefit of priority from Japanese Patent Applications No. 2010-148329filed on Jun. 29, 2010, No. 2010-148342 filed on Jun. 29, 2010 and No.2010-150471 filed on Jun. 30, 2010, of which the entire contents of allof which are incorporated herein by reference in their entirety.

BACKGROUND OF THE INVENTION

Field of the Invention

The present invention relates to a radiographic image capturingapparatus, which includes a radiation source and a radiation detectorrequired for capturing radiographic images, and which can be carried to,e.g., a patient in order to obtain radiographic image information of thepatient.

Description of the Related Art

In the medical field, there have widely been used radiographic imagecapturing apparatus, which apply radiation to a subject and guideradiation that has passed through the subject to a radiation conversionpanel (radiation detector), which captures a radiographic image fromsuch radiation. Known forms of radiation conversion panels includeconventional radiation film for recording a radiographic image by way ofexposure, and stimulable phosphor panels for storing radiation energyrepresenting a radiographic image in a phosphor, and reproducing theradiographic image as stimulated light by applying stimulating light tothe phosphor. Radiation film with the recorded radiographic image issupplied to a developing device to develop the radiographic image, orthe stimulable phosphor panel is supplied to a reading device to readthe radiographic image as a visible image.

In an operating room or the like, for the purpose of quickly andappropriately treating patients, it is necessary to read a recordedradiographic image immediately from a radiation conversion panel afterthe radiographic image has been captured. As a radiation detector whichmeets such a requirement, there have been developed a radiation detectorof a direct conversion type (electronic cassette) having a solid-statedetector for converting radiation directly into electric signals, and aradiation detector of an indirect conversion type (electronic cassette)having a scintillator for temporarily converting radiation into visiblelight and a solid-state detector for converting such visible light intoelectric signals.

In recent years, there have been growing demands for capturing an imageof a critically ill patient who cannot easily be moved out of his or herroom and also for capturing an image in emergency in an operating room.As a result, there have been increasing needs for apparatus which allowdoctors to confirm, quickly with high image quality, images that havebeen captured in clinical and surgical environments other than X-rayimage capturing rooms.

To meet such needs, a mobile radiographic image capturing apparatus hasbeen proposed. As the conventional technology of a mobile radiographicimage capturing apparatus, for example, Japanese Laid-Open PatentPublication No. 2009-201561 discloses a mobile medical cart, andJapanese Laid-Open Patent Publication No. 2010-022731 discloses aradiographic image capturing apparatus.

The mobile medical cart in Japanese Laid-Open Patent Publication No.2009-201561 and the radiographic image capturing apparatus in JapaneseLaid-Open Patent Publication No. 2010-022731 comprise a cart unit whichis movable by electric power or by hand, and a radiographic apparatusinstalled in the cart unit. The radiographic apparatus at least has anX-ray source, a cassette housing a stimulable phosphor panel whichrecords radiographic image information of a subject, an image reader forreading radiographic image information from the stimulable phosphorpanel in the cassette, and a battery for supplying electric power todevices. In particular, Japanese Laid-Open Patent Publication No.2009-201561 further discloses an example which uses an electroniccassette housing a solid-state radiation detector, instead of a cassettehousing a stimulable phosphor panel.

There has been developed a portable radiographic image capturingapparatus, which can be folded into a compact form in its entirety (seeJapanese Laid-Open Patent Publication No. 11-104117, Japanese Laid-OpenPatent Publication No. 2007-530979 (PCT), U.S. Pat. No. 4,979,198). Inaddition, radiation sources comprising field-electron-emission-typeelectron sources based on carbon nanotube (CNT) technology have alsobeen developed (see Japanese Laid-Open Patent Publication No.2007-103016, and AIST: Press Release, “Development of Portable X-raySources Using Carbon Nanostructures” [online], Mar. 19, 2009, NationalInstitute of Advanced Industrial Science and Technology, Internet<URL:http://www.aist.go.jp/aist_j/press_(—)release/pr2009/pr20090319/pr20090319.html> (hereinafter referred to as“Document 1”). It is expected that small-size, lightweight radiographicimage capturing apparatus including radiation sources will becomeavailable in the art. Further, a portable size and high energy X-raysource was developed by using LiTaO₃ that is a typical pyroelectriccrystal (see “Applying Pyroelectric Crystal to Small High Energy X-RaySource”, Advances in X-Ray Chemical Analysis, Japan, 41, 2010, pages195-200 (hereinafter referred to as “Document 2”)).

Wireless electric power transmitting schemes are known from IEDM PlenaryTalk, “Arrival of Contactless Power Transmission Sheet Expected to beEmbedded in Walls and Floors, developed by the University of Tokyo”[online], Dec. 4, 2006, Internet<URL:http://techon.nikkeibp.co.jp/article/NEWS/20061204/124943/>(hereinafter referred to as “Document 3”), and Nikkei Electronics,“Development of Wireless Power Transmission Technology, a 60-W LampTurned on in Experiment,” Dec. 3, 2007, pages 117-128 (hereinafterreferred to as “Document 4”). The process disclosed in Document 3transmits electric power based on electromagnetic induction from aprimary coil embedded in a contactless power transmission sheet. Theprocess disclosed in Document 4 is a wireless power transmissiontechnology based on magnetic field resonance between two LC resonators.

SUMMARY OF THE INVENTION

In each of the mobile medical cart disclosed in Japanese Laid-OpenPatent Publication No. 2009-201561 and the radiographic image capturingapparatus disclosed in Japanese Laid-Open Patent Publication No.2010-022731, a dedicated battery is installed. The dedicated battery isa large-sized lead battery, for example, since the battery needs toprovide electric power for energizing an X-ray source and an imagereader (or electronic cassette), or electric power for moving a medicalcart.

In this case, the following problems arise:

(1) It takes time to charge the battery.

(2) It is necessary to provide a special charging facility. For example,a hospital has such a charging facility in a basement.

(3) It is necessary to carry the medical cart to the charging facility.

(4) Since the battery is too heavy to move the medical cart by humanpower, the medical cart is electrically powered for movement. It isnecessary for the medical cart to secure electric power to return to thecharging facility, since electric power of the battery is consumed formovement. As a result, further problems arise: (a) The electric powerfor capturing a radiation image is limited; (b) It is necessary toreduce the number of images to be captured; and (c) It is impossible toattend to unexpected recapturing or additional capturing of radiographicimages.

It is conceivable to downsize a radiation source, as shown in JapaneseLaid-Open Patent Publication No. 11-104117, Japanese Laid-Open PatentPublication No. 2007-530979 (PCT), U.S. Pat. No. 4,979,198, JapaneseLaid-Open Patent Publication No. 2007-103016, and Document 1. This,however, cannot be a fundamental solution to the problems, since aconventional battery still has to be used for securing electric power ofsuch a small radiation source.

An object of the present invention is to provide a radiographic imagecapturing apparatus which is capable of supplying electric power to aradiation source and a radiation detector even outdoors, reducingconsumption of electric power, and minimizing the number batteries usedtherein, and which can be used easily and efficiently in medicalorganizations as well as other places such as accident sites, disastersites, medical checkup sites, home-care service sites, etc.

According to a first aspect of the present invention, there is provideda radiographic image capturing apparatus comprising a mobile cart unit,a plurality of devices used for capturing a radiographic image, and anelectric power supply activator enabling supply of electric powerbetween the devices, based on an instruction of permission to supplyelectric power.

According to the first aspect of the present invention, the devices mayat least comprise a radiation source device detachably attached to thecart unit, and including a radiation source for outputting radiation,and a detector device detachably attached to the cart unit, andincluding a radiation detector for detecting radiation that istransmitted through a subject in a case where the subject is irradiatedwith the radiation by the radiation source, and converting the detectedradiation into radiographic image information, and wherein the electricpower supply activator may enable the supply of electric power from theradiation source device to the detector device, or from the detectordevice to the radiation source device, based on the instruction ofpermission to supply electric power.

According to the first aspect of the present invention, the radiographicimage capturing apparatus may further comprise an electric power manageractivatable by the electric power supply activator, based on theinstruction of permission to supply electric power, wherein the devicesmay at least comprises a radiation source device detachably attached tothe cart unit, and including a radiation source for outputtingradiation, and a detector device detachably attached to the cart unit,and including a radiation detector for detecting radiation that istransmitted through a subject in a case where the subject is irradiatedwith the radiation by the radiation source, and converting the detectedradiation into radiographic image information, and wherein the electricpower manager may manage electric power required to capture a givennumber of radiographic images, and supplies the required electric powerflexibly to at least one of the radiation source device and the detectordevice.

According to the first aspect of the present invention, the devices mayat least comprise a radiation source device detachably attached to thecart unit, and including a radiation source for outputting radiation, adetector device detachably attached to the cart unit, and including aradiation detector for detecting radiation that is transmitted through asubject in a case where the subject is irradiated with the radiation bythe radiation source, and converting the detected radiation intoradiographic image information, and a controller for controlling atleast the radiation source device and the detector device, wherein theelectric power supply activator may enable supply of electric power fromthe controller to the radiation source device, or from the controller tothe detector device, based on the instruction of permission to supplyelectric power.

According to the first aspect of the present invention, the devices mayat least comprises a radiation source device detachably attached to thecart unit, and including a radiation source for outputting radiation, adetector device detachably attached to the cart unit, and including astimulable phosphor panel for detecting radiation that is transmittedthrough a subject in a case where the subject is irradiated with theradiation by the radiation source, and storing the detected radiation asradiographic image information, and an image reading apparatus forreading the radiographic image information that is stored in thestimulable phosphor panel, wherein the electric power supply activatormay enable supply of electric power from the radiation source device tothe image reading apparatus, or from the image reading apparatus to theradiation source device, based on the instruction of permission tosupply electric power.

According to the first aspect of the present invention, the radiographicimage capturing apparatus may further comprise an electric power manageractivatable by the electric power supply activator, based on theinstruction of permission to supply electric power, wherein the devicesmay at least comprise a radiation source device detachably attached tothe cart unit, and including a radiation source for outputtingradiation, a detector device detachably attached to the cart unit, andincluding a stimulable phosphor panel for detecting radiation that istransmitted through a subject in a case where the subject is irradiatedwith the radiation by the radiation source, and storing the detectedradiation as radiographic image information, and an image readingapparatus for reading the radiographic image information that is storedin the stimulable phosphor panel, and wherein the electric power managermay manage electric power required to capture a given number ofradiographic images, and supplies the required electric power flexiblyto at least one of the radiation source device and the image readingapparatus.

According to the first aspect of the present invention, the devices mayat least comprise a radiation source device detachably attached to thecart unit, and including a radiation source for outputting radiation, adetector device detachably attached to the cart unit, and including astimulable phosphor panel for detecting radiation that is transmittedthrough a subject in a case where the subject is irradiated with theradiation by the radiation source, and storing the detected radiation asradiographic image information, an image reading apparatus for readingthe radiographic image information that is stored in the stimulablephosphor panel and a controller for controlling at least the radiationsource device and the image reading apparatus, and wherein the electricpower supply activator may enable supply of electric power from thecontroller to the radiation source device, or from the controller to theimage reading apparatus, based on the instruction of permission tosupply electric power.

According to the present invention, the radiation source and theradiation detector can be supplied with electric power even if theradiographic image capturing apparatus is used outdoors. The consumptionof electric power can be reduced. Batteries that need to be included inthe radiographic image capturing apparatus are minimized. Therefore, theradiographic image capturing apparatus is convenient for use in a presetlocation such as a medical organization, an accident site, a disastersite, a medical checkup site, a home-care service site, etc.

The above and other objects, features, and advantages of the presentinvention will become more apparent from the following description whentaken in conjunction with the accompanying drawings in which preferredembodiments of the present invention are shown by way of illustrativeexample.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a perspective view of a mobile radiographic image capturingapparatus (first mobile apparatus) according to a first embodiment ofthe present invention;

FIGS. 2A to 2C are views each showing an attaching/detaching mechanismof a radiation source device to a distal end of an arm;

FIG. 3 is a perspective view of a radiographic apparatus (firstradiographic apparatus) used for the first mobile apparatus;

FIG. 4 is a perspective view showing the manner in which the firstradiographic apparatus is carried;

FIG. 5 is a horizontal cross-sectional view of the first radiographicapparatus, taken along line V-V of FIG. 3;

FIG. 6 is a cross-sectional view of the first radiographic apparatus,showing a radiation source device separated from a cassette shown inFIG. 3;

FIG. 7 is a cross-sectional view, shown partially in block form, ofinternal details of the radiation source device shown in FIG. 3;

FIG. 8 is an elevational view, partially in cross section, showing themanner in which the first radiographic apparatus captures a radiographicimage;

FIG. 9 is a perspective view showing the manner in which the firstradiographic apparatus is readied to capture radiographic images;

FIG. 10 is a perspective view showing the manner in which the firstradiographic apparatus captures a radiographic image;

FIG. 11 is a schematic view showing a pixel array of a radiationdetector of the first radiographic apparatus;

FIG. 12 is a block diagram of a circuit arrangement of the radiationdetector disposed in the cassette;

FIG. 13 is a block diagram of the first radiographic apparatus;

FIG. 14 is a block diagram partially showing a console of the firstradiographic apparatus;

FIG. 15 is a perspective view of a modification of the first mobileapparatus (in which printers are installed);

FIG. 16 is a side view, partially broken away, showing the printerinstalled in a cart unit of the first mobile apparatus;

FIG. 17 is a side view, partially broken away, showing the printerinstalled in a cassette;

FIG. 18 is a perspective view of a mobile terminal, which displays aradiographic image on a display unit thereof;

FIG. 19 is a block diagram of a battery unit;

FIG. 20 is a block diagram of a battery controller;

FIG. 21 is a block diagram of a power controller according to a firstspecific example;

FIG. 22 is a block diagram of a power controller (including a powermanager) according to a second specific example;

FIG. 23 is a block diagram of a cassette selection activator and acassette selector;

FIG. 24 is a block diagram of an integrated supply activator and anintegrated supply;

FIG. 25 is a block diagram of a power manager;

FIG. 26 is a first flowchart of an operation sequence of the firstradiographic apparatus, operated under supply timing conditions, whichare free of timing controls;

FIG. 27 is a second flowchart of an operation sequence of the firstradiographic apparatus, operated under supply timing conditions, whichare free of timing controls;

FIG. 28 is a first flowchart of an operation sequence of the firstradiographic apparatus, operated under supply timing conditions forsupplying electric power before capturing of radiographic images;

FIG. 29 is a second flowchart of an operation sequence of the firstradiographic apparatus, operated under supply timing conditions forsupplying electric power before capturing of radiographic images;

FIG. 30 is a third flowchart of an operation sequence of the firstradiographic apparatus, operated under supply timing conditions forsupplying electric power before capturing of radiographic images;

FIG. 31 is a first flowchart of an operation sequence of the firstradiographic apparatus, operated under supply timing conditions forsupplying electric power after capturing of radiographic images;

FIG. 32 is a second flowchart of an operation sequence of the firstradiographic apparatus, operated under supply timing conditions forsupplying electric power after capturing of radiographic images;

FIG. 33 is a block diagram of an electric power collector;

FIG. 34 is a flowchart of an operation sequence of the power collector;

FIG. 35 is a perspective view of a first modification of the firstradiographic apparatus;

FIG. 36 is a perspective view of a second modification of the firstradiographic apparatus;

FIG. 37 is a perspective view of a third modification of the firstradiographic apparatus;

FIG. 38 is a perspective view of a radiographic image capturingapparatus (second mobile apparatus) according to a second embodiment ofthe present invention;

FIG. 39 is a perspective view of a radiographic apparatus (secondradiographic apparatus) used for the second mobile apparatus;

FIG. 40 is a perspective view showing the manner in which the secondradiographic apparatus is carried;

FIG. 41 is a horizontal cross-sectional view taken along line XLI-XLI ofFIG. 39;

FIG. 42 is a plan view of the second radiographic apparatus, showing aradiation source device separated from a cassette shown in FIG. 39;

FIG. 43 is a cross-sectional view showing the manner in which the secondradiographic apparatus captures a radiographic image;

FIG. 44 is a view showing in greater detail a source-to-image distance(SID) that is illustrated in FIG. 43;

FIG. 45 is a perspective view showing the manner in which the secondradiographic apparatus is readied to capture radiographic images;

FIG. 46 is a perspective view showing the manner in which the secondradiographic apparatus captures a radiographic image;

FIG. 47 is a perspective view of a radiographic image capturingapparatus (third mobile apparatus) according to a third embodiment ofthe present invention;

FIG. 48 is a block diagram of an image reading apparatus;

FIG. 49 is a schematic view of the image reading apparatus;

FIG. 50 is a cross-sectional view schematically illustrating thestructure of three pixel units of a radiation detector according to amodified example of the invention; and

FIG. 51 is a view schematically illustrating the structure of a TFT anda charge storage unit shown in FIG. 50.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

Like or corresponding parts are denoted by like or correspondingreference characters throughout the views.

Embodiments of a radiographic image capturing apparatus according to thepresent invention will be described in detail below with reference toFIGS. 1 to 51.

A mobile radiographic image capturing apparatus according to a firstembodiment of the present invention, which hereinafter will be referredto as a “first mobile apparatus 1000A”, includes a cart unit 1002, atleast one portable first radiographic apparatus 10A accommodated in thecart unit 1002, a console 1004 for controlling at least the firstradiographic apparatus 10A, and an arm unit 1006 for attaching theretoor detaching therefrom a radiation source device 18 of the firstradiographic apparatus 10A.

The console 1004 comprises a notebook-shaped personal computer,including an operating unit 1008 such as a keyboard, and a display unit1010. The console 1004 is capable of sending signals to and receivingsignals from a data center (medical organization etc.) to which anoperator belongs, by way of wireless communications via a network suchas a public network or the like. Alternatively, the console 1004 may bereplaced with a mobile phone or a PDA (Personal Digital Assistant).

As shown in FIG. 2A, an attaching/detaching mechanism 1012 between theradiation source device 18 and the arm unit 1006 may be realized as amechanism using a female screw 1014 and a male screw 1016. For example,the female screw 1014 is formed on a distal end 1006 a of the arm unit1006, and the male screw 1016 is formed on a side surface of acylindrical portion 1018 that is projected on the middle of theradiation source device 18. The radiation source device 18 can beattached to the arm unit 1006 by screwing the male screw 1016 of theradiation source device 18 into the female screw 1014 of the arm unit1006, and the radiation source device 18 can be detached from the armunit 1006 by turning the radiation source device 18 in the oppositedirection.

As shown in FIG. 2B, the attaching/detaching mechanism 1012 may berealized as a mechanism using an engagement piece 1020. For example, aplurality of openings 1022 are formed on the side surface of thecylindrical portion 1018 that is projected on the middle of theradiation source device 18. In each of the openings 1022, the engagementpiece 1020 having, e.g., a triangular cross section is constantly urgedby a spring or the like to protrude outward as a protrusion. In thiscase, a protrusion amount of the engagement piece 1020 graduallyincreases toward its lower part. The engagement piece 1020 has one sidesurface that is contiguous to the oblique side of the triangular crosssection, and a bottom surface that is contiguous to the bottom side ofthe triangular cross section. On the other hand, a hole (hollow end)1024 is formed in a bottom side (distal end surface) of the distal end1006 a of the arm unit 1006 for inserting the cylindrical portion 1018of the radiation source device 18. Then, an opening 1026 is formed inthe side surface of the distal end 1006 a of the arm unit 1006 for theengagement piece 1020 (protrusion) to enter. If the cylindrical portion1018 of the radiation source device 18 is inserted into the hole 1024 inthe distal end surface of the arm unit 1006, the engagement piece 1020enters the opening 1026 of the arm unit 1006, and thus the radiationsource device 18 is attached to the arm unit 1006. Conversely, if theengagement piece 1020 is pushed inwardly against the spring force or thelike, the engagement piece 1020 is released from the engagement with aninner wall of the opening 1026 of the arm unit 1006, and the radiationsource device 18 can be detached from the arm unit 1006.

Alternatively, as shown in FIG. 2C, the attaching/detaching mechanism1012 may be realized using a magnet, provided that the magnet does notaffect the generation of radiation. For example, a metal piece 1028 isapplied to a top surface of the cylindrical portion 1018 that isprojected on the middle of the radiation source device 18, while amagnet sheet 1030 is applied to a distal end surface 1006 b of the armunit 1006. If the metal piece 1028 on the top surface of the cylindricalportion 1018 of the radiation source device 18 is brought into contactwith the magnet sheet 1030 on the distal end surface 1006 b of the armunit 1006, the radiation source device 18 is attached to the arm unit1006 by magnetic attraction. Conversely, the radiation source device 18can be detached easily from the arm unit 1006 by separating them fromeach other against the magnetic attraction.

As shown in FIG. 1, the cart unit 1002 has a plurality of wheels 1032,and is movable by human power using a handle 1034. Alternatively, thecart unit 1002 can be electrically powered for movement. The cart unit1002 also has a plurality of slots 1036 for accommodating respectivepieces of the first radiographic apparatus 10A. Each piece of the firstradiographic apparatus 10A may have the same size or a different size.

As shown in FIG. 3, the first radiographic apparatus 10A includes acassette 12 having a substantially rectangular outer contour shaped as ahousing, and which is made of a material permeable to radiation 46 (seeFIG. 8), and the cylindrical radiation source device 18 held in thecassette 12 by a pair of holders 16 a, 16 b, which project outwardlyfrom opposite ends of one side 14 a of the cassette 12. A radiationsource device 18 of a first radiographic apparatus 10A can be replacedwith a radiation source device 18 of another first radiographicapparatus 10A. Also, a cassette 12 of a first radiographic apparatus 10Acan be replaced with a cassette 12 of another first radiographicapparatus 10A.

The cassette 12 has crisscross guide lines 22 disposed on a surface(irradiated surface) 20 thereof, which serve as a reference for an imagecapturing area and an image capturing position. The cassette 12 also hasa grip 24 on another side 14 b thereof remote from the one side 14 a.The cassette 12 has two other sides 14 c, 14 d extending perpendicularto and between the sides 14 a, 14 b, which are opposite to each other.On the side 14 c, there are disposed a USB (Universal Serial Bus)terminal 28 as an interface means for sending information to andreceiving information from an external device, a card slot 32 forinsertion of a memory card 30 therein, and an unlocking button 34 to bedescribed later. The side 14 c also supports thereon a mobile terminal42, which is detachable from the cassette 12. The mobile terminal 42includes a display unit 36 and an operating unit 40 having a number ofcontrol buttons operable by a doctor or radiological technician(hereinafter referred to as an “operator”) 38 who handles the firstradiographic apparatus 10A. The radiation source device 18 has anexposure switch 48, which can be operated by the operator 38 in order tocause a radiation source 44 (see FIG. 8), which shall be descried later,to start emitting radiation 46.

FIGS. 3 and 4 show the first radiographic apparatus 10A, which is takenout from the slots 1036 of the cart unit 1002 by the operator 38. Inthis state, the radiation source device 18 and the cassette 12 areintegrally joined to each other.

As shown in FIG. 1, the operator 38 moves the cart unit 1002 toward asubject 50 whose radiographic images are to be captured (including avictim at the accident site or the disaster site, or an examinee at themedical checkup site, or a person receiving home-care services at home).Then, the operator 38 takes out the first radiographic apparatus 10Afrom the cart unit 1002, and separates the cassette 12 from theradiation source device 18. Thereafter, the radiation source device 18is attached to the distal end 1006 a of the arm unit 1006. If recumbentimage capturing is to be carried out, for example, the cassette 12 isdisposed between the subject 50 and a bed 1040 or a sheet (blanketetc.). Then, the operator 38 turns on an electric power supply switch(ON operation). The ON operation of the electric power supply switchincludes the clicking of the left button of a mouse on an iconrepresenting an electric power supply switch shown on the display unit1010 of the console 1004. Alternatively, the ON operation may beperformed using an operation switch on the cart unit 1002 that isdedicated for electric power supply operation. Accordingly, at anabove-mentioned site or the like, radiographic images of the subject 50can be captured using the first radiographic apparatus 10A.

If the radiation source device 18 and the cassette 12 are joined to eachother integrally, they are secured together by a joining mechanism 82(see FIG. 5), to be described later, so that the first radiographicapparatus 10A can be carried by the operator 38.

Next, the portable first radiographic apparatus 10A will be described indetail below with reference to FIGS. 5 to 19.

As shown in FIG. 5, the sides 14 a, 14 b, 14 c, 14 d of the cassette 12are constituted by respective side walls 52 a, 52 b, 52 c, 52 d. The USBterminal 28, the card slot 32, and the unlocking button 34 are providedon the side wall 52 c. The side wall 52 c has a recess 54, which isdefined between the card slot 32 and the unlocking button 34. The mobileterminal 42 (see FIG. 3) can be placed in the recess 54.

If the unlocking button 34 is pressed by the operator 38 (see FIG. 4),the unlocking button 34 is displaced along the side wall 52 a toward theside wall 52 d. A slide 56 projects along the side wall 52 a from asurface of the unlocking button 34 that faces the side wall 52 d, and aspring 60 acts between the slide 56 and a tooth 58 that projectsinwardly from the side wall 52 a. The spring 60 normally biases theunlocking button 34 to move in a direction from the tooth 58 toward theside wall 52 c. The side wall 52 a has a through hole 62 defined in aportion thereof against which the slide 56 slides, the through hole 62extending from an inner surface of the side wall 52 a to an outersurface thereof. The slide 56 has a hook 64, which extends through thethrough hole 62.

As shown in FIGS. 5 and 6, the radiation source device 18 has a throughhole 66 defined therein at a location aligned with the through hole 62of the cassette 12 in a case where the radiation source device 18 isheld in the cassette 12 by the holders 16 a, 16 b. The through hole 66is of substantially the same size as the through hole 62. In a casewhere the hook 64 is displaced toward the side wall 52 c under the biasof the spring 60, the hook 64 engages with an edge of the through hole66 and locks the radiation source device 18 in place, thereby integrallyjoining the radiation source device 18 to the cassette 12 (see FIG. 5).

The radiation source device 18 has an electrically conductive connectionterminal (first radiation source connection terminal) 68 a mounted on anend thereof that faces the holder 16 a, and also has an electricallyconductive connection terminal (second radiation source connectionterminal) 68 b mounted on another end thereof that faces the holder 16b. The first connection terminal 68 a is convex in shape toward theholder 16 a, whereas the second connection terminal 68 b is concave inshape toward the holder 16 b. The radiation source device 18 has a firstenergy input/output unit 300, or a second energy input/output unit 302(see FIG. 19) for inputting and outputting electric power through acontact (wired or the like) link or a contactless (wireless or the like)link, for example. The first radiation source connection terminal 68 aand the second radiation source connection terminal 68 b, for example,constitute the first energy input/output unit 300 or the second energyinput/output unit 302, respectively, and may be electrically connectedthrough a wireless link. The first energy input/output unit 300 or thesecond energy input/output unit 302 is mounted on a side wall of theradiation source device 18 (see FIG. 3).

The holder 16 a of the cassette 12 has an electrically conductiveconnection terminal (first cassette connection terminal) 70 a on asurface thereof that faces the radiation source device 18. The holder 16b of the cassette 12 has an electrically conductive connection terminal(second cassette connection terminal) 70 b on a surface thereof thatfaces the radiation source device 18. The first connection terminal 70 ais concave, complementary in shape to the first convex connectionterminal 68 a, whereas the second connection terminal 70 b is convex,complementary in shape to the second concave connection terminal 68 b.The cassette 12 has a first energy input/output unit 300 or a secondenergy input/output unit 302 (see FIG. 19) for inputting and outputtingelectric power through a contact (wired or the like) link or acontactless (wireless or the like) link, for example. The first cassetteconnection terminal 70 a and the second cassette connection terminal 70b, for example, constitute the first energy input/output unit 300 or thesecond energy input/output unit 302, and may be electrically connectedthrough a wireless link. The first energy input/output unit 300 or thesecond energy input/output unit 302 is mounted on the side 14 c of thecassette 12.

As shown in FIG. 5, in a case where the hook 64 engages the edge of thethrough hole 66 under the resiliency of the spring 60 in order to keepthe radiation source device 18 and the cassette 12 joined integrallywith each other, the first convex connection terminal 68 a and the firstconcave connection terminal 70 a engage with each other, and the secondconcave connection terminal 68 b and the second convex connectionterminal 70 b engage with each other, respectively. Therefore, theradiation source device 18 and the cassette 12 are securely andintegrally joined with each other. Consequently, the connectionterminals 68 a, 68 b, 70 a, 70 b function as members for assisting thehook 64 and the through hole 66 in maintaining the radiation sourcedevice 18 and the cassette 12 in an integrally joined condition.

As shown in FIG. 6, in a case where the operator 38 presses theunlocking button 34 to move the unlocking button 34 toward the side wall52 d against the resiliency of the spring 60, the hook 64 and the slide56 are displaced toward the side wall 52 d, so as to bring the hook 64out of engagement with the edge of the through hole 66. While the hook64 is kept out of engagement with the edge of the through hole 66, i.e.,while the operator 38 presses the unlocking button 34, the operator 38can remove or separate the radiation source device 18 from the cassette12, whereby the radiation source device 18 and the cassette 12 arereleased from each other. The released radiation source device 18 isattached to the distal end of the arm unit 1006 shown in FIG. 1.

The cassette 12 houses therein a tape measure 72 comprising a ribbon 76marked with graduations 74, which is coiled into a roll by a spring, notshown, in the tape measure 72. The tape measure 72 is combined with arotary encoder 78 on one side thereof, for detecting the length by whichthe ribbon 76 is reeled out from the tape measure 72. The ribbon 76,which is reeled out from the tape measure 72, extends through a hole 80that is defined in the side wall 52 a at a location facing the tapemeasure 72, and a distal end of the ribbon 76 is fixed to the radiationsource device 18 near the second connection terminal 68 b.

In a case where the radiation source device 18 and the cassette 12 arejoined integrally with each other as shown in FIG. 5, most of the ribbon76 is coiled into a roll inside the tape measure 72 under the resiliencyof the spring. On the other hand, in a case where the radiation sourcedevice 18 and the cassette 12 are not joined integrally with each other,as shown in FIGS. 6 through 10, the ribbon 76 can be pulled out of thetape measure 72 through the hole 80 by separating the radiation sourcedevice 18 away from the cassette 12 against the resiliency of thespring.

The unlocking button 34, the slide 56, the spring 60, the hook 64, theconnection terminals 68 a, 68 b, 70 a, 70 b, and the tape measure 72jointly make up a joining mechanism 82 for integrally joining theradiation source device 18 and the cassette 12 with each other in a casewhere the first radiographic apparatus 10A is carried, and also forenabling the radiation source device 18 and the cassette 12 to beseparated from each other in a case where the first radiographicapparatus 10A is utilized to capture radiographic images.

The tape measure 72 comprises the ribbon 76, which is marked withgraduations 74 in the illustrated embodiment. However, as a functionalequivalent to the ribbon 76, the tape measure 72 may comprise a stringmarked with graduations 74.

As shown in FIGS. 5 and 8, the cassette 12 also houses therein a grid 84for removing scattered rays of radiation 46 from the subject 50 in acase where the radiation source 44 applies radiation 46 with respect tothe subject 50, a radiation detector 86 for detecting radiation 46 thathas passed through the subject 50, and a lead plate 88 for absorbingback scattered rays of radiation 46, which are successively arranged inthis order from the irradiated surface 20 of the cassette 12. Theirradiated surface 20 of the cassette 12 may also be constructed as thegrid 84.

The radiation detector 86 may comprise a radiation detector (including afront surface reading type and a rear surface reading type) of anindirect conversion type, including a scintillator for convertingradiation 46 that has passed through the subject 50 into visible light,and solid-state detectors (hereinafter also referred to as pixels) madeof amorphous silicon (a-Si) or the like for converting the visible lightinto electric signals. A radiation detector of ISS (Irradiation SideSampling) type as a front surface reading type, comprises solid-statedetectors and a scintillator that are successively provided along anirradiation direction of the radiation 46. A radiation detector of PSS(Penetration Side Sampling) type as a rear surface reading type,comprises a scintillator and solid-state detectors that are successivelyprovided along the irradiation direction of the radiation 46. As well asthe above-described indirect conversion type, the radiation detector 86may comprise a radiation detector of a direct conversion type,comprising solid-state detectors made of amorphous selenium (a-Se) orthe like for converting a dose of radiation 46 directly into electricsignals.

As shown in FIG. 5, the cassette 12 also houses therein a battery unit304 as a power supply for the cassette 12, a battery controller 306 forlimiting and controlling supply of electric power to the battery unit304, a cassette controller 92 for controlling the radiation detector 86(see FIG. 8) with electric power supplied from the battery unit 304, anda transceiver 94 for sending and receiving signals including informationconcerning radiation 46 that is detected by the radiation detector 86,to and from an external circuit. A plate of lead or the like shouldpreferably be placed over the side surfaces of the cassette controller92 and the transceiver 94 under the irradiated surface 20 in order toprotect the cassette controller 92 and the transceiver 94 againstdamage, which would otherwise be caused if the cassette controller 92and the transceiver 94 were irradiated with radiation 46.

The battery unit 304 supplies electric power to the rotary encoder 78,the radiation detector 86, the cassette controller 92, and thetransceiver 94 in the cassette 12. The battery unit 304 can also chargethe mobile terminal 42 in a case where the mobile terminal 42 is placedin the recess 54. As shown in FIG. 19, the battery unit 304 includes, inaddition to the first energy input/output unit 300 and the second energyinput/output unit 302, a battery (electric power storage unit) 308, afirst energy converter 310, and a second energy converter 312. Thebattery unit 304 can be supplied with (i.e., charged by) electric powerfrom an external circuit, or can supply electric power to an externalcircuit, over a wired or wireless link via the first energy input/outputunit 300 and/or the second energy input/output unit 302. That is,contact or contactless electric power supply is available. A firstswitcher 314 a is connected between the first energy input/output unit300 and the first energy converter 310. A second switcher 314 b isconnected between the second energy input/output unit 302 and the secondenergy converter 312. Third through fifth switchers 314 c through 314 eare connected between the battery 308 and the first energy input/outputunit 300 and the second energy input/output unit 302.

The first energy converter 310 comprises a first input converter 316 anda first output converter 318. The second energy converter 312 comprisesa second input converter 320 and a second output converter 322. Forinputting electric power via the first energy input/output unit 300, thefirst switcher 314 a electrically connects the first energy input/outputunit 300 and the first input converter 316 to each other, while thethird switcher 314 c and the fifth switcher 314 e electrically connectthe first input converter 316 and the battery 308 to each other.Conversely, for outputting electric power via the first energyinput/output unit 300, the first switcher 314 a electrically connectsthe first energy input/output unit 300 and the first output converter318 to each other, while the third switcher 314 c and the fifth switcher314 e electrically connect the first output converter 318 and thebattery 308 to each other. Similarly, for inputting electric power viathe second energy input/output unit 302, the second switcher 314 belectrically connects the second energy input/output unit 302 and thesecond input converter 320 to each other, while the fourth switcher 314d and the fifth switcher 314 e electrically connect the second inputconverter 320 and the battery 308 to each other. Conversely, foroutputting electric power via the second energy input/output unit 302,the second switcher 314 b electrically connects the second energyinput/output unit 302 and the second output converter 322 to each other,while the fourth switcher 314 d and the fifth switcher 314 eelectrically connect the second output converter 322 and the battery 308to each other. The first through fifth switchers 314 a through 314 e arecontrolled by an electric power supply controller 374, to be describedlater, in order to make such connections.

The first energy input/output unit 300, the second energy input/outputunit 302, the first energy converter 310, and the second energyconverter 312 have different structures depending on the type of energyto be supplied (supplied energy).

For example, if electric energy is supplied through wired connectionssuch as cables, connection terminals, etc., then the first energyinput/output unit 300 comprises a connector, which is connected tocables and connection terminals. The first input converter 316 comprisesa voltage converter or the like for converting a voltage applied fromthe first energy input/output unit 300 through the first switcher 314 ainto a voltage that is optimum for charging the battery 308. The firstoutput converter 318 comprises a voltage converter or the like forconverting a voltage output from the battery 308 through the fifthswitcher 314 e and the third switcher 314 c into a voltage that isoptimum for power transmission. The second energy input/output unit 302and the second energy converter 312 also are of a similar construction.

If electric energy is supplied by way of electromagnetic inductionthrough a coil (primary coil or secondary coil) embedded in acontactless power transmission sheet, for example as disclosed inDocument 3, then the first energy input/output unit 300 comprises asecondary coil or a primary coil, whereas the first input converter 316comprises a voltage converter or the like for converting a voltagegenerated by the first energy input/output unit 300, which functions asa secondary coil, into a voltage that is optimum for charging thebattery 308. Further, the first output converter 318 comprises avoltage-to-current converter for converting a voltage output from thebattery 308 through the fifth switcher 314 e and the third switcher 314c into a current that flows to the first energy input/output unit 300,which functions as a primary coil. The second energy input/output unit302 and the second energy converter 312 also are of a similarconstruction.

If electric energy is supplied by way of wireless power transmissiontechnology based on magnetic resonance as disclosed in Document 4, thenthe first energy input/output unit 300 comprises a second LC resonatoror a first LC resonator, which is combined with a first LC resonator ora second LC resonator of an electric power transmitter, whereas thefirst input converter 316 comprises a coil, i.e., a secondary coilcombined with a primary coil as the coil of the second LC resonator, forconverting electromagnetic energy generated by the first energyinput/output unit 300, which functions as the second LC resonator.Further, the first output converter 318 comprises a coil, i.e., aprimary coil combined with a secondary coil as the coil of the first LCresonator, for outputting a voltage output from the battery 308 throughthe fifth switcher 314 e and the third switcher 314 c as electromagneticenergy from the first energy input/output unit 300, which functions asthe first LC resonator. The second energy input/output unit 302 and thesecond energy converter 312 also are of a similar construction.

The supplied energy may be optical energy or thermal energy. If thesupplied energy is optical energy, then an energy receiver is provided,which comprises a photodetector for detecting optical energy, and anenergy converter is provided, which comprises a photoelectric transducer(photoelectric converter) for converting the detected optical energyinto electric power. If the supplied energy is thermal energy, then anenergy receiver is provided, which comprises a thermal sensor fordetecting thermal energy, and an energy converter is provided, whichcomprises a thermoelectric transducer, i.e., a thermoelectric transducerbased on the Seebeck Effect, for converting the detected thermal energyinto electric power.

The battery 308 may comprise a secondary battery, such as a nickelhydrogen battery, a nickel cadmium battery, a lithium battery, or thelike, or a capacitor, such as a catalytic capacitor, an electricdouble-layer capacitor, a lithium ion capacitor, or the like. Thebattery 308 may be detachably mounted on the cassette 12. The battery308 may comprise a small-size built-in capacitor, which is capable ofstoring an amount of electric power required to capture at least oneradiographic image.

Since the transceiver 94 is capable of sending signals to and receivingsignals from an external circuit, the transceiver 94 can send signals toand receive signals from a transceiver 98 (see FIG. 13) of the mobileterminal 42, which is removed from the recess 54, and also can sendsignals to and receive signals from a transceiver 100 of the radiationsource device 18, which is separated from the cassette 12. Even if thecassette 12 and the radiation source device 18 are integrally coupled toeach other and/or if the mobile terminal 42 is placed in the recess 54,the transceiver 94 can send signals to and receive signals from thetransceivers 98, 100.

As shown in FIG. 7, the radiation source device 18 houses therein theradiation source 44, a battery unit 304, a battery controller 306 forcontrolling the battery unit 304, a transceiver 100, a radiation sourcecontroller 102 for controlling the radiation source 44, and a laserpointer 104. The first energy input/output unit 300 and the secondenergy input/output unit 302, which are identical to those provided onthe cassette 12, are mounted on a side wall of the casing of theradiation source device 18.

The radiation source 44 comprises a field-electron-emission-typeradiation source, which is similar to the field-electron-emission-typeradiation source disclosed in Japanese Laid-Open Patent Publication No.2007-103016.

The radiation source 44 includes a disk-shaped rotary anode 110 mountedon a rotational shaft 108, which can be rotated about its axis by arotating mechanism 106, an annular target layer 112 disposed on thesurface of the rotary anode 110 and made up principally from a metallicelement such as Mo or the like, a cathode 114 disposed in confrontingrelation to the rotary anode 110, and a field-electron-emission-typeelectron source 116 disposed on the cathode 114 in confronting relationto the target layer 112.

In a case where the operator 38 operates the exposure switch 48, theradiation source controller 102 controls the radiation source 44 tooutput radiation 46. More specifically, in a case where the radiationsource 44 is controlled by the radiation source controller 102, therotating mechanism 106 rotates the rotational shaft 108 so as to rotatethe rotary anode 110. The battery unit 304 supplies electric power to apower supply 118, which applies a negative voltage to thefield-electron-emission-type electron source 116. The battery unit 304also supplies electric power to a power supply 120, which applies avoltage between the rotary anode 110 and the cathode 114. Morespecifically, a positive voltage is applied to the rotary anode 110,whereas a negative voltage is applied to the cathode 114. Thefield-electron-emission-type electron source 116 emits electrons, whichare accelerated and bombard the target layer 112 due to the voltageapplied between the rotary anode 110 and the cathode 114. The electronsare focused onto a focus point 122 on the surface of the target layer112, and the bombarded surface of the target layer 112 emits radiation46 from the focus point 122 at an intensity level depending on theapplied electrons. As the radiation source 44, a portable size and highenergy X-ray source that is disclosed in Document 2 and uses a crystalof tourmaline, LiNbO₃, LiTaO₃, ZnO, and the like, may be employed. Inthis case, for example, about 100 kV voltage can be generated by usingLiNbO₃, whose axial length is 1 cm.

For irradiating the subject 50 with radiation 46 in order to captureradiographic images of the subject 50, it is necessary first to performa preparatory procedure, thus readying the first radiographic apparatus10A for capturing radiographic images. The preparatory procedureincludes a process for presetting a source-to-image distance (SID),which represents the distance (imaging distance) between the focus point122 of the radiation source 44 and a position 124 (see FIG. 8) on theradiation detector 86 located directly beneath the focus point 122, anda process for bringing the center of a range within which the irradiatedsurface 20 is irradiated with radiation 46 into alignment with a centralposition 126, i.e., a point of intersection, of the aforementionedcrisscross guide lines 22.

The preparatory procedure is carried out as follows. As shown in FIGS. 8and 9, while the radiation source device 18 is separated from thecassette 12, the operator 38 pulls the ribbon 76 from the tape measure72 until the length of the ribbon 76, which is reeled out from the tapemeasure 72, is equal to a reeled-out length 11 that depends on the SID.The laser pointer 104 is controlled by the radiation source controller102 to apply and focus a laser beam 128 on the irradiated surface 20, inorder to display a crisscross mark 130 on the irradiated surface 20,which represents the center of a range within which the irradiatedsurface 20 is irradiated with radiation 46.

The SID, the reeled-out length 11 that depends on the SID, and adistance 12 between the position 124 or the central position 126 and theside 14 a, which has the hole 80 through which the ribbon 76 is pulledout, are related to each other according to the equationSID≈(11²−12²)^(1/2). The distance 12 is constant.

After the ribbon 76 has been pulled out from the tape measure 72 by thereeled-out length 11, the operator 38 positionally adjusts the radiationsource device 18 so as to bring the mark 130 displayed on the irradiatedsurface 20 into alignment with the central position 126. Thereafter, theoperator 38 turns on the exposure switch 48 to cause the radiationsource 44 to apply radiation 46 to the subject 50 on the irradiatedsurface 20, thereby capturing radiographic images of the subject 50, asshown in FIG. 10. In FIG. 10, an example is shown in which aradiographic image of a hand of the subject 50 is captured.

As shown in FIG. 11, the radiation detector 86 comprises a number ofpixels 132 arrayed on a substrate, not shown, a number of gate lines 134for supplying control signals to the pixels 132, and a number of signallines 136 for reading electric signals output from the pixels 132.

A circuit arrangement of the radiation detector 86, which is of anindirect conversion type, for example, that is housed in the cassette12, will be described in detail below with reference to FIG. 12.

As shown in FIG. 12, the radiation detector 86 comprises an array ofthin-film transistors (TFTs) 140 arranged in rows and columns, and aphotoelectric conversion layer 138 including the pixels 132, and made ofa material such as amorphous silicon (a-Si) or the like for convertingvisible light into analog electric signals. The photoelectric conversionlayer 138 is disposed on the array of TFTs 140. In a case whereradiation 46 is applied to the radiation detector 86, the pixels 132generate electric charges by converting visible light into analogelectric signals. Then, in a case where the TFTs 140 are turned on onerow at a time, electric charges are read from the pixels 132 as imagesignals.

The TFTs 140 are connected respectively to the pixels 132. The gatelines 134, which extend parallel to the rows, and the signal lines 136,which extend parallel to the columns, are connected to the TFTs 140. Thegate lines 134 are connected to a line scanning driver 142, and thesignal lines 136 are connected to a multiplexer 144. The gate lines 134are supplied with control signals Von, Voff from the line scanningdriver 142 for turning on and off the TFTs 140 along the rows. The linescanning driver 142 comprises a plurality of switches SW1 for switchingbetween the gate lines 134, and an address decoder 146 for outputting aselection signal for selecting one of the switches SW1 at a time. Thecassette controller 92 supplies an address signal to the address decoder146.

The signal lines 136 are supplied with electric charges stored by thepixels 132 through the TFTs 140 arranged in the columns. The electriccharges supplied to the signal lines 136 are amplified by amplifiers148, which are connected respectively to the signal lines 136. Theamplifiers 148 are connected through respective sample and hold circuits150 to the multiplexer 144. The multiplexer 144 comprises a plurality ofswitches SW2 for successively switching between the signal lines 136,and an address decoder 152 for outputting selection signals forselecting one of the switches SW2 at a time. The address decoder 152 issupplied with an address signal from the cassette controller 92. Themultiplexer 144 has an output terminal connected to an A/D converter154. Radiographic image signals, which are generated by the multiplexer144 based on electric charges from the sample and hold circuits 150, areconverted by the A/D converter 154 into digital image signalsrepresenting radiographic image information, which is supplied to thecassette controller 92.

The TFTs 140, which function as switching devices, may be combined withanother image capturing device, such as a CMOS (ComplementaryMetal-Oxide Semiconductor) image sensor or the like. Alternatively, theTFTs 140 may be replaced with a CCD (Charge-Coupled Device) image sensorfor shifting and transferring electric charges with shift pulses thatcorrespond to gate signals in the TFTs.

FIG. 13 shows in block form the first radiographic apparatus 10A.Components of the first radiographic apparatus 10A, which have not beendescribed above with reference to FIGS. 3 through 12, will mainly bedescribed below with reference to FIG. 13.

The cassette controller 92 comprises an address signal generator 162, animage memory 164, and an SID determining unit (imaging distancedetermining unit) 168.

The address signal generator 162 supplies address signals to the addressdecoder 146 of the line scanning driver 142, as well as to the addressdecoder 152 of the multiplexer 144. The image memory 164 stores theradiographic image information detected by the radiation detector 86.

The SID determining unit 168 calculates the imaging distance between thefocus point 122 and the position 124, in a case where the radiationsource device 18 is tentatively placed over the irradiated surface 20according to the present reeled-out length 11 of the ribbon 76, based onthe reeled-out length 11 of the ribbon 76, which is input from therotary encoder 78, and the stored distance 12.

If the calculated imaging distance agrees with the SID, the SIDdetermining unit 168 controls the display unit 36 through thetransceivers 94, 98, so as to display information representing thepresent reeled-out length of the ribbon 76 as the reeled-out length 11that depends on the SID, and also to display information representingthat the imaging distance agrees with the SID. The cassette 12 mayinclude a mechanism for preventing (locking) the ribbon 76 from beingreeled out further, in a case where the reeled-out length 11 and theimaging distance have been determined to agree with the SID. If thecalculated imaging distance does not agree with the SID, then the SIDdetermining unit 168 controls the display unit 36 through thetransceivers 94, 98 in order to display information representing thedifference between the present reeled-out length and the reeled-outlength 11, and also to display information representing that the imagingdistance does not agree with the SID.

The SID determining unit 168, the rotary encoder 78, and the tapemeasure 72 jointly make up an imaging distance setting means 169.

The cassette controller 92 can transmit cassette ID information of thecassette 12 and radiographic image information, which are stored in theimage memory 164, via the transceiver 94 to the mobile terminal 42 byway of wireless communications.

A printer 170 a may be installed in the radiation source device 18 forprinting the data from the radiation source controller 102. Also, aprinter 170 b may be installed in the cassette 12 for printing the datafrom the cassette controller 92. Usually, for a printer of medical use,there is a thermal printer for a transparent manuscript (first printer)or an ink-jet printer for a reflective manuscript (second printer). Ifthe second printer is used as the printer 170 a and the printer 170 b,the radiation source device 18 and the cassette 12 using the same can bedownsized. Both the first and second printers consume large electricpower. For the first printer, especially, a thermal head printer will beused if it should be downsized (see, e.g., Japanese Laid-Open PatentPublication No. 10-051635), but electric power consumption may beextremely large. Therefore, if the electric power supply is controlledsuch that the remaining levels of electric power stored in the batteries308 in the devices are utilized flexibly, which will be described later,then a printer having large electric power consumption may be used asthe printer 170 a or the printer 170 b.

The first mobile apparatus 1000A is carried (moved) to an accident ordisaster site, as well as a patient room in the hospital or a home of aperson (patient) receiving home-care services. In the accident site andthe like, the first mobile apparatus 1000A may be contaminated by dust,mud, or dirty water. In the cassette 12 and the radiation source device18 of the first radiographic apparatus 10A, at least a portionsurrounding an electric system thereof is often sealed. Therefore,contactless electric power supply through wireless connections or thelike is desirable for an electric power supply method, compared tocontact electric power supply by wired connections or the like.

The console 1004 has a power supply switch, speakers, a microphone, andother accessories, similar to those of ordinary notebook-shaped personalcomputers. The console 1004 incorporates therein a transceiver 288 (seeFIG. 14) for sending information to and receiving information from anexternal device such as a network, the radiation source device 18, thecassette 12, or the like. The console 1004 also includes, on a side wallthereof, a first energy input/output unit 300, and a second energyinput/output unit 302. In this case, the first energy input/output unit300 of the console 1004 is connected by a cable to the first energyinput/output unit 300 of the radiation source device 18 of the firstradiographic apparatus 10A, while the second energy input/output unit302 of the console 1004 is connected by a cable to the first energyinput/output unit 300 of the cassette 12 of the first radiographicapparatus 10A. However, the first energy input/output unit 300 and thesecond energy input/output unit 302 may be connected wirelessly(referred to as a “wireless connection”, or a connection in a wirelessfashion, etc.) in an area, where the first radiographic apparatus 10Acan utilize wireless electric power supply.

The console 1004 includes therein a battery unit 304 and a batterycontroller 306, which are identical to those of the cassette 12 and theradiation source device 18.

A printer 170 c may be installed in the first mobile apparatus 1000A forprinting the data from the console 1004. For the printer 170 c, theaforementioned first or second printer may be used. In this case, also,as described later, if the electric power supply is controlled such thatthe remaining levels of electric power stored in the batteries 308 inthe devices are utilized flexibly, which will be described later, then aprinter having large electric power consumption may be used.

For example, the printer 170 c installed in the cart unit 1002 and theprinter 170 b installed in the cassette 12 will be described below withreference to FIGS. 15 through 17.

First, the printer 170 c installed in the cart unit 1002 is a device, inwhich using a recording material that does not require wet developmentprocessing, the recording material is exposed by means of scanningexposure with light beams composed of laser light to form a latentimage, then heat developed to obtain a visible image, and followed bycooling to the ordinary temperature. As shown in FIG. 15, the printer170 c has a recording material loading section 176 on a side surface ofthe cart unit 1002, for loading a recording material cartridge 174 inwhich a recording material 172 (see FIG. 16) is housed. The recordingmaterial 172 wound in a rolled shape is accommodated in the recordingmaterial cartridge 174.

As shown in FIG. 16, the printer 170 c is basically provided with arecording material feed section 178, an image exposure section 180 asrecording means, a heat development section 182, and a cooling section184 in the order of the feed direction of the recording material 172.Also, the printer 170 c is provided with feed means for feeding therecording material 172, and a printer control section 186 for drivingand controlling the respective sections. The feed means are provided atimportant points among the respective sections.

The recording material feed section 178 is provided with the recordingmaterial loading section 176 (see FIG. 15), a feed roller pair 188, anda cutter 190. The recording material cartridge 174 is loaded detachablyinto the recording material loading section 176 shown in FIG. 15. Forthe recording material cartridge 174, plural kinds of cartridges areprepared depending upon the size of the recording material 172 to beaccommodated (for example, B4 (257×364 mm), HANSETSU (14×17 inch),MUTSUGIRI (8×10 inch), and the like). As shown in FIG. 15, the recordingmaterial cartridge 174 has a size identification symbol on a sidethereof for visually confirming the size of the recording material 172loaded therein easily, such as “B4” for the recording material 172 of B4size, “H” for the recording material 172 of the HANSETSU size, “M” forthe recording material 172 of the MUTSUGIRI size, and the like. Inloading the recording material cartridge 174 into the recording materialloading section 176 corresponding to the size, size information is inputinto the printer control section 186 manually by an operator 38 (e.g.,using an operating unit 1008), or by detecting a bar code 192 attachedto the outer surface of the cartridge 174 by a recognition sensor (notshown) within the recording material loading section 176.

In the recording material cartridge 174, a case thereof is formed so asto have sealing properties, the inside thereof forms an accommodationspace of the rolled recording material 172, and this accommodation spaceis opened to an outlet 174 a. That is, the tip end of the recordingmaterial 172 on the sending-out side is drawn out from the outlet 174 a.

The tip end portion drawn out from the outlet 174 a of the recordingmaterial cartridge 174 is sandwiched by a feed roller pair 188 and issent out from the recording material cartridge 174 by rotation of thefeed roller pair 188. The cutter 190 is aligned in the downstream sideof the recording material feed direction of the feed roller pair 188 andcuts the recording material 172 sent out by the feed roller pair 188into a prescribed length. Cutting of the recording material 172 iscarried out by detecting the sending-out length of the recordingmaterial 172 from the rotation amount of the feed roller pair 188 or bya non-illustrated sensor and controlling the actuation of the cutter 190by the printer control section 186 based on the detected value.

The image exposure section 180 scans and exposes the recording material172 having been fed from the recording material feed section 178 withlight beams L in the major scanning direction (substantiallyperpendicular to the feed direction of the recording material 172) andfeeds the recording material 172 in the sub-scanning direction (the feeddirection of the recording material 172), thereby recording a desiredimage (e.g., radiographic image information) on the recording material172 to form a latent image.

The heat development section 182 heats a recording material to beheated, to which heat treatment is applied. With respect to theconstruction of the heat development section 182, one or more plateheaters 194 are lined in the feed direction of the recording material172, as heating bodies which will reach a temperature necessary forprocessing the recording material 172.

In the heat development section 182 including the heaters 194, therecording material 172 is slipped and relatively moved while beingbrought into contact with the upper surface of each plate heater 194. Inthis case, as feed means of the recording material 172, a feed roller196 and a plurality of press rollers 198 which also function to achieveheat conduction into the recording material 172 from each plate heater194, are aligned. As the press rollers 198, a metal roller, a resinroller, a rubber roller, and the like can be utilized. Non-illustrateddischarge rollers for feeding the recording material 172 are aligned atthe terminal of the feed path within the heat development section 182.

The recording material 172 having been fed out from the heat developmentsection 182 is cooled in the cooling section 184 while being fed by thecooling roller pairs 200. The recording material 172 discharged from thecooling section 184 is guided into a guide plate 202 provided on the wayof the feed path and further discharged into a discharge tray 206 from adischarge roller pair 204. The operator 38 can visually confirm theimage (e.g., radiographic image information) recorded on the recordingmaterial 172 having a prescribed length and discharged from thedischarge tray 206. Further, since the printer 170 c is theaforementioned first printer, a printed image has such a high imagequality that interpretation of radiogram can be performed.

Incidentally, as shown in FIGS. 15 and 17, the printer 170 b is housedin a installation space 208 in a housing 14 of a cassette 12, which ispositioned close to a side 14 b having a grip 24 thereon. An opening 210is provided in the housing 14, for example, at a position close to theside 14 b on the irradiated surface 20, for sending out the tip end ofthe recording material 172 from the housing 14. The recording material172 is replaceably received in the installation space 208. Further, thegrip 24 (grip unit 25) may be detachable from the cassette 12. In thiscase, the printer 170 b may also be detachable from the cassette 12together with the grip unit 25. For example, the printer 170 b may bedetachably attached to the cassette 12 using hooks 211 and the like.FIG. 17 shows that the hooks 211 formed on the printer 170 b engage thecassette 12. For detaching the printer 170 b, the portions of theprinter 170 b that are close to the hooks 211 are pushed alongdirections indicated by dashed arrows 212. Then, the engagement of thehooks 211 with the cassette 12 can be released.

The printer 170 b has a supply roller pair 213 for sending out the tipend of the recording material 172, a print head 214 for printing adesired image (e.g., radiographic image information) on the recordingmaterial 172, a feed roller pair 216 for feeding to the opening 210 therecording material 172 on which an image or the like is printed, and acutter 218 for cutting the recording material 172 into a prescribedlength. For the print head 214, a print head for an ink-jet printer or athermal printer may be used. Since the printer 170 b is theaforementioned second printer, the printer 170 b can be used forcarrying out diagnosis in emergency or checking images for confirmation,though the image quality thereof is not so high as that of the firstprinter. Also, the printer 170 b may be used for printing the characterinformation of image capturing conditions, the character information ofpatient information, the character information of positional informationbased on GPS, and the like. Meanwhile, for the printer 170 a of theradiation source device 18, the structure in the aforementioned printer170 b of the cassette 12 may be used.

A preparatory procedure using the cassette 12 and the radiation sourcedevice 18, as well as operations of the first radiographic apparatus 10Ato capture radiographic images, shall be described below.

First, the operator 38 performs an operation to ready the firstradiographic apparatus 10A for capturing radiographic images at a sitewhere the first radiographic apparatus 10A has been carried. Theoperator 38 operates the operating unit 40 of the mobile terminal 42 (orthe operating unit 1008 of the console 1004) in order to register imagecapturing conditions including subject information (e.g., SID) of thesubject 50 to be imaged.

In this case, the operator 38 operates the operating unit 40 while themobile terminal 42 either is detached from or placed within the recess54. If the body region to be imaged and an image capturing method areknown, then the operator 38 also operates the operating unit 40 in orderto register the body region and the image capturing method as imagecapturing conditions. If details of the subject 50 are already knownbefore the operator 38 carries the first radiographic apparatus 10A tothe imaging site, then the operator 38 may register the subjectinformation including such details using the mobile terminal 42, whichis located at the data center, e.g., medical organization or the like,where the subject 50 is being treated.

In this way, in a case where the operator 38 operates the operating unit40 of the mobile terminal 42 (or the operating unit 1008 of the console1004), the registered image capturing conditions, including subjectinformation of the subject 50, are sent from the transceiver 98 of themobile terminal 42 to the transceiver 94 of the cassette 12 by way ofwireless communications, whereupon the image capturing conditions areregistered in the cassette controller 92.

In a case where the operator 38 presses the unlocking button 34, thehook 64 is displaced toward the side wall 52 d against the resiliency ofthe spring 60 until the hook 64 is brought out of engagement with theedge of the through hole 66.

In a case where the operator 38 detaches the radiation source device 18from the cassette 12 while the hook 64 does not engage with the edge ofthe through hole 66, i.e., while the operator 38 presses the unlockingbutton 34, then the connection terminal 68 a becomes disengaged from theconnection terminal 70 a, and the connection terminal 68 b becomesdisengaged from the connection terminal 70 b, thereby releasing theradiation source device 18 and the cassette 12 from each other.

The operator 38 sets the imaging distance and then brings the mark 130,which is displayed on the irradiated surface 20, into alignment with thecentral position 126 of the guide lines 22. Thereafter, the operator 38places and positions the subject 50 between the irradiated surface 20and the radiation source device 18.

The operator 38 moves the radiation source device 18, whereby the ribbon76 is reeled out from the tape measure 72 until the actual reeled-outlength of the ribbon 76 reaches the reeled-out length 11 that depends onthe SID.

The ribbon 76 is reeled out from the tape measure 72 until the actualreeled-out length of the ribbon 76 reaches the reeled-out length 11, inaccordance with either of the two processes described below.

According to the first process, the SID determining unit 168automatically determines whether or not the actual reeled-out length ofthe ribbon 76 has reached the reeled-out length 11. Therefore, theoperator 38 is able to reel out the ribbon 76 from the tape measure 72until the actual reeled-out length of the ribbon 76 reaches thereeled-out length 11 that depends on the SID.

In the first process, the rotary encoder 78 detects the actualreeled-out length of the ribbon 76, and based on the detected reeled-outlength, the SID determining unit 168 calculates the imaging distancebetween the focus point 122 and the position 124 in a case where theradiation source device 18 is tentatively placed over the irradiatedsurface 20 in accordance with the present reeled-out length of theribbon 76.

If the imaging distance agrees with the SID, then the SID determiningunit 168 controls the display unit 36 via the transceivers 94, 98 todisplay information representing the reeled-out length of the ribbon 76,and also to display information representing that the imaging distanceagrees with the SID. If the imaging distance does not agree with theSID, then the SID determining unit 168 controls the display unit 36 viathe transceivers 94, 98 to display information representing thedifference between the present reeled-out length and the reeled-outlength 11, and also to display information representing that the imagingdistance does not agree with the SID.

The first process allows the operator 38 to set the imaging distanceeasily, because the operator 38 may reel out the ribbon 76 from the tapemeasure 72 according to the information displayed on the display unit36.

According to the second process, the reeled-out length 11 already isknown, and the operator 38 reels out the ribbon 76 from the tape measure72, while observing the graduations 74, until the present reeled-outlength reaches the reeled-out length 11.

After the ribbon 76 has been reeled out from the tape measure 72 untilthe present reeled-out length reaches the reeled-out length 11 thatdepends on the SID, the operator 38 moves the radiation source device 18so as to confront (i.e., be placed in a facing relationship with) theirradiated surface 20.

In this case, the radiation source controller 102 controls the laserpointer 104 to apply a laser beam 128 to the irradiated surface 20. Thecrisscross mark 130, which represents the center of a range within whichthe irradiated surface 20 is irradiated with radiation 46, is displayedon the irradiated surface 20. The operator 38 positionally adjusts theradiation source device 18 until the mark 130 and the central position126 are aligned with each other.

After having adjusted the position of the radiation source device 18until the mark 130 and the central position 126 are aligned with eachother, the operator 38 places or positions the subject 50 on theirradiated surface 20, so that the center of a body region of thesubject 50 to be imaged is aligned with the central position 126, i.e.,is aligned with the position of the mark 130.

After the above positional adjustment has been made, the radiationsource device 18 is secured at the adjusted position by a holder, notshown, for example.

At a site such as a disaster site, due to limited space availability,the first radiographic apparatus 10A may not be able to captureradiographic images with the desired SID. Therefore, the cassettecontroller 92 may recalculate image capturing conditions based on a newSID, which is different from the desired SID, and store the recalculatedimage capturing conditions together with the new SID in association withimage data, or transmit the new SID and/or the recalculated imagecapturing conditions via a network to a data center for confirmation.

After the subject 50 has been positioned, the operator 38 turns on theexposure switch 48 to begin capturing radiographic images of the subject50.

In a case where the exposure switch 48 is turned on, the radiationsource controller 102 sends a request for image capturing conditions tothe cassette controller 92 by way of wireless communications. Based onsuch a request, the cassette controller 92 sends the image capturingconditions (control signals) with respect to the body region of thesubject 50 to be imaged to the radiation source device 18. In a casewhere the radiation source controller 102 receives the image capturingconditions, the radiation source controller 102 controls the laserpointer 104 in order to stop emitting the laser beam 128, and controlsthe radiation source 44 to apply radiation 46 at a predetermined dose tothe subject 50.

In the radiation source 44, the rotating mechanism 106 is controlled bythe radiation source controller 102 in order to rotate the rotationalshaft 108 and the rotary anode 110. The power supply 118 applies anegative voltage to the field-electron-emission-type electron source116, and the power supply 120 applies a voltage between the rotary anode110 and the cathode 114, based on electric power supplied from thebattery unit 304. The field-electron-emission-type electron source 116emits electrons, which are accelerated by the voltage applied betweenthe rotary anode 110 and the cathode 114, and the electrons bombard thetarget layer 112. The surface of the target layer 112, which isbombarded with electrons, emits radiation 46 from the focus point 122,the intensity of which depends on the applied electrons.

While the subject 50 is irradiated with radiation 46 for a givenirradiation time based on the image capturing conditions, the radiation46 passes through the subject 50 and reaches the radiation detector 86of the cassette 12.

Since the radiation detector 86 is of an indirect conversion type, thescintillator of the radiation detector 86 emits visible light having anintensity that depends on the intensity of the radiation 46, and thepixels 132 of the photoelectric conversion layer 138 convert the visiblelight into electric charges and store the electric charges. The electriccharges stored by the pixels 132, which are representative of aradiographic image of the subject 50, are read from the pixels 132according to address signals, which are supplied from the address signalgenerator 162 of the cassette controller 92 to the line scanning driver142 and the multiplexer 144.

More specifically, in response to an address signal supplied from theaddress signal generator 162, the address decoder 146 of the linescanning driver 142 outputs a selection signal in order to select one ofthe switches SW1, which supplies the control signal Von to the gates ofthe TFTs 140 that are connected to the gate line 134 corresponding tothe selected switch SW1. In response to address signals supplied fromthe address signal generator 162, the address decoder 152 of themultiplexer 144 outputs selection signals to successively turn on theswitches SW2 so as to switch between the signal lines 136, for therebyreading through the signal lines 136 the electric charges stored in thepixels 132 that are connected to the selected gate line 134.

The electric charges, which are read from the pixels 132 connected tothe selected gate line 134, are amplified respectively by the amplifiers148, sampled by the sample and hold circuits 150, and supplied to themultiplexer 144. Based on the supplied electric charges, the multiplexer144 generates and supplies radiographic image signals to the A/Dconverter 154, which converts the radiographic image signals intodigital signals. Digital signals representative of the radiographicimage information are stored in the image memory 164 of the cassettecontroller 92.

Similarly, the address decoder 146 of the line scanning driver 142successively turns on the switches SW1 so as to switch between the gatelines 134 according to the address signals supplied from the addresssignal generator 162. Electric charges stored in the pixels 132connected to the successively selected gate lines 134 are read throughthe signal lines 136, processed by the multiplexer 144, and convertedinto digital signals by the A/D converter 154. The digital signals arestored in the image memory 164 of the cassette controller 92.

Radiographic image information represented by the digital signals storedin the image memory 164 is transmitted through the transceiver 94 to themobile terminal 42 by way of wireless communications. Radiographic imageinformation transmitted to the mobile terminal 42 is received by thetransceiver 98, and is transmitted from the transceiver 98 to thedisplay unit 36, which displays a radiographic image based on theradiation image information, as shown in FIG. 18. The operator 38 candetermine whether or not the body region of the subject 50 to be imagedhas been appropriately imaged by confirming the radiographic imagedisplayed on the display unit 36.

For example, if the radiographic image displayed on the display unit 36does not include the body region of the subject 50 to be imaged, thenthe operator 38 judges that the subject 50 has not been appropriatelyimaged, and captures another radiographic image of the subject 50. Inthis case, using the mobile terminal 42, the operator 38 updates thenumber of captured images in the image capturing conditions, byincrementing the number with the number of recaptured images.

The radiographic image displayed on the display unit 36 may be of aquality that is sufficient enough to determine whether or not thesubject 50 has been appropriately imaged. The displayed radiographicimage may either be a radiographic image represented by the radiographicimage information stored in the image memory 164, an image of raw data,or a relatively low resolution processed image.

The battery controller 306 will be described below with reference toFIGS. 20 through 25.

As shown in FIG. 20, the battery controller 306 comprises a memory 330,an electric power supply activator 336 for activating an electric powercontroller 334 according to supply timing conditions, the electric powercontroller 334 for enabling supply of electric power between thebatteries 308 (see FIG. 19) of the devices that are connected in a wiredor wireless fashion, an electric power supply limiter 338 for limitingthe supply of electric power by the electric power controller 334 duringthe period in which a radiographic image is being captured, and a pauseprocessor 340 for temporarily pausing the electric power controller 334when a necessary image capturing process is completed or when the supplyof electric power is completed.

The memory 330 stores ID information for identifying the devicesincorporating the battery controller 306, i.e., the cassette 12, theradiation source device 18, etc., and also stores various conditions.The memory 330 also temporarily stores various table information, whichmay be entered via a network, the mobile terminal 42, etc.

Turning on the power supply, the electric power supply activator 336 isactivated. If the supply timing conditions stored in the memory 330 arefree of timing controls, then the electric power supply activator 336 ofa device whose electric power supply switch has been operated activatesthe corresponding electric power controller 334 based on operation ofthe electric power supply switch. The electric power supply activator336 may activate the electric power controller 334 without waiting forthe electric power supply switch to be operated. In such a case, if aninterlock process is not performed, then the electric power controllers334 of all the devices whose power supply is turned on are activated,thus tending to cause processing operations to interfere with eachother. Therefore, the electric power supply activator 336 of each of thedevices refers to interlock information registered in the memory 330,i.e., the ID of the radiation source device 18 or the cassette 12 to beused in a preset image capturing process, and only the electric powersupply activator 336 of a device whose ID is identical to the ID of theinterlock information activates the corresponding electric powercontroller 334. Thus, for example, only the electric power controller334 of the radiation source device 18 that is used in the preset imagecapturing process is operated, while interference from the other devicesis prevented.

If the supply timing conditions indicate supply of electric power beforecapturing of radiographic images, then the electric power controller 334is activated based on the image capturing conditions (order) that areinput from the mobile terminal 42. In this case, only the electric powersupply activator 336 of a device having an ID identical to that of theID of the radiation source device 18 or the cassette 12 to be used tocapture radiographic images, which is registered in advance in the imagecapturing conditions, activates the corresponding electric powercontroller 334. If the supply timing conditions indicate supply ofelectric power after capturing of radiographic images, then the electricpower controller 334 is activated based on an image capture completionsignal supplied from an image capture completion determiner 386 (seeFIG. 21). In this case as well, only the electric power supply activator336 of a device having an ID identical to that of the ID of theradiation source device 18 or the cassette 12 to be used to captureradiographic images, which is registered in advance in the imagecapturing conditions, activates the corresponding electric powercontroller 334.

The electric power controller 334 is available in differentconfigurations according to two specific examples, i.e., a firstspecific example and a second specific example. According to the firstspecific example, as shown in FIG. 21, the battery 308 of the radiationsource device 18 supplies electric power to the battery 308 of thecassette 12, or the battery 308 of the radiation source device 18controls supply of electric power to the battery 308 of the cassette 12.As shown in FIG. 21, the electric power controller 334 according to thefirst specific example comprises, as functional components thereof, adevice connection detector 360, a cassette selector activator 362, acassette selector 364, an integrated supply activator 366, an integratedsupply 368, an electric power supply route setting unit 370, anamount-of-supplied-electric-power setting unit 372, an electric powersupply controller 374, a remaining level detector 376, an image captureinterruption instructing unit 378, a counter 380, a re-supplyinstructing unit 382, an image capture permission instructing unit 384,an image capture completion determiner 386, and an electric power supplycompletion output unit 388.

According to the second specific example, the electric power controller334 controls supply of electric power such that the remaining levels ofelectric power stored in the batteries 308 of the connected devices areutilized flexibly between the connected devices, based on preset batterycharging conditions and image capturing conditions. As shown in FIG. 22,the electric power controller 334 according to the second specificexample comprises, in addition to the functional components as describedabove, an electric power manager 390 and functional components ancillaryto the electric power manager 390, which include a remaining levelprediction updater 392, a usage history updater 394, a remaining levelinformation transfer unit 396, and a usage history transfer unit 398.

Flexible utilization of the remaining levels of electric power stored inthe batteries 308 between the connected devices implies at least thefollowing aspects:

(1) One or more devices, the batteries of which store an excessiveremaining level of electric power, supply electric power to a devicewhose battery stores a remaining level of electric power that is notsufficient to capture radiographic images.

(2) One or more devices, which are not used to capture radiographicimages, supply electric power required to capture radiographic images tothe aforesaid device, which is used to capture radiographic images.

(3) One or more devices, which are not used to capture radiographicimages, supply electric power required to capture radiographic images tothe aforesaid device, which is used to capture radiographic images,while increasing the remaining level of electric power in the battery ofthe aforesaid device, i.e., the amount of electric power held by theaforesaid device, up to at least a level required to captureradiographic images.

As shown in FIG. 22, the electric power controller 334 limits supply ofelectric power during a period in which the electric power controller334 is supplied with a supply limit signal, which is input thereto fromthe electric power supply limiter 338. Limiting supply of electric powerrefers to stopping supply of electric power, reducing the amount ofelectric power supplied per unit time, or controlling supply of electricpower in a stepwise manner. To stop supply of electric power, as shownin FIG. 19, the electric power controller 334 may output a stop signalto the electric power supply controller 374, thereby causing theelectric power supply controller 374 to relay-control the first throughfifth switchers 314 a through 314 e in order to change to neutralpositions thereof, which are neither input positions nor outputpositions, for example. In order to reduce the amount of electric powersupplied per unit time, the electric power controller 334 may output asupplied-amount reduction signal to the electric power supply controller374, thereby causing the electric power supply controller 374 to reducethe amount of electric power supplied per unit time to a preset level.In order to control the supply of electric power in a stepwise manner,as described later, the electric power controller 334 may stop supplyingelectric power while electric charges are being stored in the pixels inthe cassette 12 and are converted from analog signals into digitalsignals, supply a small amount of electric power while image data arebeing transferred, and supply a large amount of electric power during anidling period after transferring of the image data is completed. Theelectric power controller 334 stops controlling supply of electric powerbased on a pause signal, which is input from the pause processor 340,and waits to be activated at a subsequent time by the electric powersupply activator 336.

According to the first specific example, as shown in FIG. 19, forexample, the device connection detector 360 detects whether the device(radiation source or cassette) is connected to at least one of the firstenergy input/output unit 300 and the second energy input/output unit 302in a wired or wireless fashion. A wireless connection is detected by,for example, an obstacle sensor such as an ultrasonic sensor or thelike, which determines whether the device (radiation source device 18 orcassette 12) has entered into an area in which the device can besupplied with electric power wirelessly from the first energyinput/output unit 300 and the second energy input/output unit 302. Asshown in FIG. 23, the cassette selector activator 362 activates thecassette selector 364 if a condition concerning a route, from amongbattery charging conditions stored in the memory 330, represents onlysupply of electric power from one cassette 12 to the radiation sourcedevice 18, the aforesaid device is the radiation source device 18, andconnection of a plurality of cassettes 12 to the radiation source device18 is detected.

The cassette selector 364 comprises a cassette ID acquirer 400, acassette information acquirer 402, and a selector 404.

The cassette ID acquirer 400 sends a transfer request for requestingthat the cassettes 12, which are connected to the radiation sourcedevice 18, transfer IDs thereof. The cassettes 12 output IDs to theradiation source device 18 based on the transfer request. The cassetteID acquirer 400 acquires the IDs and stores the IDs in the memory 330.

The cassette information acquirer 402 acquires cassette informationtables, which contain information concerning defective pixels, etc., andusage history tables corresponding to the acquired IDs via the network.

The selector 404 selects a cassette 12 that matches selecting conditionsfrom among the connected cassettes 12 based on the selecting conditions,the acquired cassette information tables, and the acquired usage historytables, which are stored in the memory 330. The selector 404 thenoutputs the ID of the selected cassette 12 to the electric power supplyroute setting unit 370.

The selecting conditions for selecting a cassette 12 include:

(1-a) a large-size cassette 12;

This condition serves the purpose of discharging electric power from alarge-size cassette 12 in a special environment where no large-sizecassette 12 is used. The size of a cassette 12 is determined based onsize information that is recorded in the cassette information table.

(1-b) a small-size cassette 12;

This condition serves the purpose of preferentially discharging electricpower from a cassette 12 that is less versatile.

(1-c) a cassette 12 with many defective pixels;

This condition serves the purpose of preferentially discharging electricpower from a cassette 12 that is less frequently used, therebypreventing the cassette 12 from becoming disabled substantiallysimultaneously. The number of defective pixels is determined based oninformation concerning defective pixels recorded in the cassetteinformation table. The information concerning defective pixels, which isrecorded in the cassette information table, is regularly or irregularlyupdated upon calibration or the like, for example.

(1-d) a cassette 12 with a small imaging area;

The size of an imaging area is calculated from information concerningdefective pixels, which is recorded in the cassette information table,particularly positional information about the defective pixels.

(1-e) a cassette 12 with a highly deteriorated battery 308;

(1-f) a cassette 12 with a lowly deteriorated battery 308;

The level of deterioration of the battery 308 is determined based on thenumber of times that the cassette 12 has been used, which is recorded inthe cassette information table.

(1-g) a cassette 12 that has been used many times;

The number of times that the cassette 12 has been used is determinedbased on a counted number of times that the cassette 12 has been used,which is recorded in the cassette information table, or based oninformation concerning an accumulated radiation dose, which is recordedin the cassette information table.

(1-h) a cassette 12 with a small remaining built-in memory capacity;

The remaining built-in memory capacity is determined based on a reply,which is sent from the cassette controller 92 in response to an inquiryas to the remaining built-in memory capacity sent to the cassettecontroller 92.

(1-i) a cassette 12 that is positioned a small distance from theradiation source device 18;

This condition serves the purpose of selecting a cassette 12 that caneasily supply electric power over a small distance, thereby reducing theburden on the circuits involved.

The distance from the radiation source device 18 to the cassette 12 isdetermined based on the information concerning present positions of thecassettes 12 acquired via GPS, or distance information from a rangesensor such as an ultrasonic sensor, a three-dimensional magneticsensor, or the like.

As shown in FIG. 24, the integrated supply activator 366 activates theintegrated supply 368 if a condition concerning a route, from among thebattery charging conditions stored in the memory 330, represents onlysupply of electric power from a plurality of cassettes 12 to theradiation source device 18, the aforesaid device is the radiation sourcedevice 18, and connection of a plurality of cassettes 12 to theradiation source device 18 is detected.

The integrated supply 368 comprises a cassette ID acquirer 400, acassette information acquirer 402, and a weighting setting unit 406.

The cassette ID acquirer 400 sends a transfer request for requestingthat cassettes 12 connected to the radiation source device 18 transferIDs thereof. The cassettes 12 output IDs to the radiation source device18 based on the transfer request. The cassette ID acquirer 400 acquiresthe IDs and stores the IDs in the memory 330.

The cassette information acquirer 402 acquires cassette informationtables, which contain information concerning defective pixels, etc., andusage history tables corresponding to the acquired IDs via the network.

The weighting setting unit 406 sets weighting coefficients forrespective amounts of electric power to be supplied from the cassettes12 to the radiation source device 18, based on integrating conditions,the acquired cassette information tables, and the acquired usage historytables, which are stored in the memory 330. The weighting setting unit406 then outputs the set weighting coefficients, together withcorresponding ID information, to the amount-of-supplied-electric-powersetting unit 372.

The integrating conditions include:

(2-a) The amount of supplied electric power is sorted depending on theamount of defective pixels;

As the number of defective pixels becomes greater, the weighting settingunit 406 sets a weighting coefficient for increasing the amount ofsupplied electric power. Conversely, as the number of defective pixelsbecomes smaller, the weighting setting unit 406 sets a weightingcoefficient for reducing the amount of supplied electric power.

(2-b) The amount of supplied electric power is sorted depending on theimaging area;

As the imaging area becomes smaller, the weighting setting unit 406 setsa weighting coefficient for increasing the amount of supplied electricpower. Conversely, as the imaging area becomes greater, the weightingsetting unit 406 sets a weighting coefficient for reducing the amount ofsupplied electric power.

(2-c) The amount of supplied electric power is sorted depending on thelevel of deterioration of the battery 308;

As the level of deterioration of the battery 308 becomes greater, theweighting setting unit 406 sets a weighting coefficient for increasingthe amount of supplied electric power. Conversely, as the level ofdeterioration of the battery 308 becomes smaller, the weighting settingunit 406 sets a weighting coefficient for reducing the amount ofsupplied electric power.

(2-d) The amount of supplied electric power is sorted depending on thenumber of times that the cassette 12 has been used;

As the number of times that the cassette 12 has been used becomesgreater, the weighting setting unit 406 sets a weighting coefficient forincreasing the amount of supplied electric power. Conversely, as thenumber of times that the cassette 12 has been used is smaller, theweighting setting unit 406 sets a weighting coefficient for reducing theamount of supplied electric power.

(2-e) The amount of supplied electric power is sorted depending on theremaining built-in memory capacity;

As the amount of supplied electric power becomes smaller, the weightingsetting unit 406 sets a weighting coefficient for increasing the amountof supplied electric power. Conversely, as the amount of suppliedelectric power becomes greater, the weighting setting unit 406 sets aweighting coefficient for reducing the amount of supplied electricpower.

(2-f) The amount of supplied electric power is sorted depending on thedistance to the radiation source device 18.

As the distance to the radiation source device 18 becomes smaller, theweighting setting unit 406 sets a weighting coefficient for increasingthe amount of supplied electric power. Conversely, as the distance tothe radiation source device 18 becomes greater, the weighting settingunit 406 sets a weighting coefficient for reducing the amount ofsupplied electric power.

Then, the electric power supply route setting unit 370 sets a route forsupply of electric power based on a condition concerning the route fromamong the battery charging conditions stored in the memory 330. Forexample, the electric power supply route setting unit 370 sets a routefrom the radiation source device 18 to the cassette 12, or a route fromthe cassette 12 to the radiation source device 18. If the electric powersupply route setting unit 370 is supplied with an ID from the cassetteselector 364, then the electric power supply route setting unit 370 setsa route from the cassette 12 to the radiation source device 18corresponding to the ID. If the electric power supply route setting unit370 is supplied with a plurality of IDs from the integrated supply 368,then the electric power supply route setting unit 370 sets routes fromthe cassettes 12 to the radiation source device 18 corresponding to suchIDs. Route information representing the set IDs is displayed on thedisplay unit 1010 of the console 1004 or a display screen of the mobileterminal 42. The condition concerning the route is descriptive of atleast one source of electric power. If the source of electric power isthe radiation source device 18, then the radiation source device 18supplies electric power to the cassette 12. If the source of electricpower is the cassette 12, then the cassette 12 supplies electric powerto the radiation source device 18. The condition concerning the routecan be changed as desired by the mobile terminal 42. If the re-supplyinstructing unit 382 provides a re-supply instruction, i.e., if there-supply instructing unit 382 inputs a re-supply instruction signal tothe electric power supply route setting unit 370, then the electricpower supply route setting unit 370 sets the route for supply ofelectric power based on battery charging conditions. If the operator 38intends to additionally charge the battery of another device, e.g., theradiation source device 18 or the cassette 12, then the operator 38enters the route for supply of electric power to the other device, i.e.,a route from the other device to the radiation source device 18 or thecassette 12 that is used to capture radiographic images, or a route fromthe radiation source device 18 or the cassette 12 that is used tocapture radiographic images to the other device, and also enters anamount of electric power to be supplied. Based on the entered route forsupply of electric power, the electric power supply route setting unit370 outputs a supply source instruction signal or a supply destinationinstruction signal to the electric power supply controller 374 of eachdevice.

The amount-of-supplied-electric-power setting unit 372 sets an amount ofelectric power to be supplied based on a condition concerning the amountof electric power to be supplied, from among the battery chargingconditions. At least items such as a full battery charge, an amount ofelectric power to be supplied that is required to capture a singleradiographic image, etc., can be used as conditions concerning theamount of electric power to be supplied. One of such items, which isselected at present, is applicable as the condition concerning theamount of electric power to be supplied. An item to be applied can beselected as desired by the mobile terminal 42. An amount of electricpower to be supplied can be set as a numerical value by the mobileterminal 42. If the amount-of-supplied-electric-power setting unit 372is supplied with a plurality of IDs and corresponding coefficients fromthe integrated supply 368, then the amount-of-supplied-electric-powersetting unit 372 multiplies the amount of electric power to be suppliedby such coefficients in order to set amounts of electric power to besupplied respectively from the cassettes 12 to the radiation sourcedevice 18. If the re-supply instructing unit 382 provides a re-supplyinstruction, then the amount-of-supplied-electric-power setting unit 372sets an amount of electric power to be supplied based on a conditionconcerning the amount of electric power to be supplied, from among thebattery charging conditions. The amount of electric power to be suppliedcan also be changed as desired by the mobile terminal 42. If batteriesof devices are to be charged as well, then theamount-of-supplied-electric-power setting unit 372 also sets respectiveamounts of electric power to be supplied in order to charge thebatteries, and supplies the set amounts of electric power to be suppliedto the electric power supply controllers 374 of each of the respectivedevices.

As shown in FIG. 19, if a supply source instruction signal is input tothe electric power supply controller 374, then the electric power supplycontroller 374 controls the battery 308 in order to output electricpower. If a supply destination instruction signal is input to theelectric power supply controller 374, then the electric power supplycontroller 374 controls the battery 308 in order to receive electricpower. Based on a remaining level of electric power in the battery 308,which is detected by the remaining level detector 376, the electricpower supply controller 374 controls the battery 308 that is suppliedwith electric power at a constant charging rate, or controls the battery308 to supply electric power at the constant discharging rate. Assumingthat the amount of electric power to be supplied is small, then theelectric power supply controller 374 can quickly charge or discharge thebattery 308. If the remaining level of electric power in the battery308, which is detected by the remaining level detector 376, isinsufficient to capture a single radiographic image, then the electricpower supply controller 374 outputs an imaging disable signal, whichincludes the remaining level of electric power and the ID of theaforesaid device. In a case where the supply of electric power to thebattery 308 or the supply of electric power from the battery 308 iscompleted, the electric power supply controller 374 outputs a supplytermination signal.

As described above, the remaining level detector 376 detects a remaininglevel of electric power in the battery 308, and sends a signalrepresentative of the detected remaining level of electric power in thebattery 308 to the electric power supply controller 374.

The image capture interruption instructing unit 378, as shown in FIG.21, outputs a message representing interruption of an image capturingprocess to the mobile terminal 42, based on an imaging disabled signalinput from the electric power supply controller 374.

The counter 380 counts the number of times that the exposure switch 48has been turned on. The counter 380 resets the count (count=0) based onan image capture completion signal, which is input from the imagecapture completion determiner 386.

Based on the imaging disabled signal input from the electric powersupply controller 374, the re-supply instructing unit 382 outputs are-supply instruction signal including the preset count of the counter380, the amount of electric power included in the imaging disabledsignal, and the ID of the aforesaid device, respectively, to theelectric power supply route setting unit 370, theamount-of-supplied-electric-power setting unit 372, and the electricpower manager 390. If electric power is supplied after capturing ofradiographic images, since the electric power controller 334 itself isnot activated, the re-supply instructing unit 382 of the radiationsource device 18 or the cassette 12 that is used to capture radiographicimages activates the electric power supply route setting unit 370, theamount-of-supplied-electric-power setting unit 372, and the electricpower manager 390, using an interrupt routine for emergency.

If the supply timing conditions recorded in the memory 330 are free oftiming controls, or indicate supply electric power before capturing ofradiographic images, then the image capture permission instructing unit384 outputs an image capture permission message to the mobile terminal42 based on supply termination signals, which are input from theelectric power supply controllers 374 of all of the devices to whichelectric power is supplied.

The image capture completion determiner 386 compares the number of timesthat radiographic images have been captured in the image capturingconditions with the count of the counter 380, and outputs an imagecapture completion signal when the number of times that radiographicimages have been captured becomes equal to the count.

The electric power supply completion output unit 388 outputs an electricpower supply completion signal based on supply termination signals,which are input from the electric power supply controllers 374 of all ofthe devices to which electric power is supplied.

The electric power supply limiter 338 shown in FIG. 20 determineswhether or not a radiographic image of the subject 50 is being capturedif the supply timing conditions recorded in the memory 330 include acondition indicating that “the supply of electric power is stopped whilea radiographic image is being captured.” If a radiographic image isbeing captured, then the electric power supply limiter 338 outputs asupply limit signal during the period in which a radiographic image isbeing captured. More specifically, when the exposure switch 48 is turnedon, the electric power supply limiter 338 outputs a supply limit signal.Thereafter, when a predetermined period of time has elapsed, theelectric power supply limiter 338 stops outputting the supply limitsignal. The electric power controller 334 limits supply of electricpower during the period in which the supply limit signal is inputthereto.

The period during which the electric power supply limiter 338 outputsthe supply limit signal should preferably be any one of a period(storage period) in which radiation 46 having passed through the subject50 is applied to the radiation detector 86 and converted by ascintillator (not shown) into visible light, and the visible light isconverted at each pixel 132 into electric signals that are stored aselectric charges (signal charges), a period (reading period) duringwhich the stored electric charges are read, and a period(analog-to-digital conversion period) during which the read electriccharges (analog signals) are converted into digital signals by the A/Dconverter 154, a period which is a combination of the above periods, ora period that includes all the above periods. In the above threeperiods, the image signals (radiographic image information) are highlysusceptible to noise. More specifically, in the storage period and thereading period, since the level of electric charge is very low, theradiographic image information is highly susceptible to noise. In theanalog-to-digital conversion period, analog signals are less resistantto noise than digital signals, and any noise added to the analog signalstends to be converted into digital signals and appear in the image data.

The storage period includes a period during which the radiation source44 emits radiation 46. More specifically, after the storage period hasstarted, the radiation source 44 begins to emit radiation 46 as quicklyas possible, and after the radiation source 44 has stopped emittingradiation 46, the stored electric charges are read immediately from thepixels. Any time lag associated with these processes should be reducedas much as possible in order to reduce dark current, and hence increasethe quality of radiographic images that are generated. The readingperiod refers to a period during which the TFTs 140 are turned on, andsignals are supplied through the amplifiers 148 to the A/D converter154. The reading period and the analog-to-digital conversion periodoccur substantially at the same time, although the reading time startsslightly earlier than the analog-to-digital conversion period.

The period during which the supply limit signal is output should extendfrom a time when the supply limit signal is output to a time when theradiation source device 18 stops emitting radiation 46, or morepreferably reside within the period during which the radiographic imageis captured, so that the cassette 12 can detect radiation 46 with highquality. A predicted time, which is required to capture and display aradiographic image, may be preset and used as the period during whichthe supply limit signal is output. The degree to which the amount ofsupplied electric power is reduced per unit time may be setexperimentally to a value for preventing noise from being added to theradiographic image, or for reducing any added noise to a level that isnot detrimental to the quality of the radiographic image.

If the supply timing conditions recorded in the memory 330 are free oftiming controls, or indicate supply of electric power before capturingof radiographic images, then the pause processor 340 shown in FIG. 20outputs a pause signal to the electric power controller 334, based on animage capture completion signal input from an image capture completiondeterminer 386. If the supply timing conditions recorded in the memory330 indicate supply of electric power after capturing of radiographicimages, then the pause processor 340 outputs a pause signal to theelectric power controller 334, based on an electric power supplycompletion signal input from the electric power supply completion outputunit 388.

According to the second specific example, the electric power manager 390shown in FIG. 22 gives the electric power supply controller 374information for controlling supply of electric power, such that theremaining levels of electric power stored in the batteries 308 of thedevices are utilized flexibly between the devices, based onpredesignated battery charging conditions and image capturingconditions. The electric power manager 390 is incorporated in theradiation source device 18 and/or the cassette 12. As shown in FIG. 25,the electric power manager 390 comprises an ID acquirer 410, aninformation acquirer 412 for acquiring various information, anamount-of-consumed-electric-power predictor 414, and an informationupdater 416.

The ID acquirer 410 sends a transfer request for requesting the devicethat incorporates the electric power manager 390 therein and anotherdevice that is connected to the device to transfer respective IDsthereof. Based on the transfer request, the devices output their IDsrespectively to the electric power manager 390. The ID acquirer 410acquires the IDs input thereto and registers the acquired IDs in thememory 330. If another radiation source device 18 or another cassette12, in addition to the radiation source device 18 and the cassette 12used to capture radiographic images, are connected or are present in anarea in which they can be fed wirelessly, then the ID acquirer 410 alsoacquires IDs of the other radiation source device 18 and the cassette12.

The information acquirer 412 for acquiring various information acquirespresent or previous image capturing conditions, which are input via themobile terminal 42 or the network, remaining level-of-electric-energyinformation tables corresponding to the IDs, previous image capturingconditions corresponding to the IDs, and usage history tablescorresponding to the IDs, and stores such information in the memory 330.

The amount-of-consumed-electric-power predictor 414 calculates amountsof electric power that are consumed by the radiation source device 18and the cassette 12 used to capture radiographic images, from thebattery charging conditions stored in the memory 330 and the present orprevious image capturing conditions representative of the number ofradiographic images to be captured, mAs values, etc. Theamount-of-consumed-electric-power predictor 414 then corrects thecalculated amounts of electric power by multiplying the calculatedamounts by usage histories of the radiation source device 18 and thecassette 12, i.e., coefficients corresponding to the number of timesthat the radiation source device 18 and the cassette 12 have been used,thereby predicting amounts of electric power that will be consumed bythe radiation source device 18 and the cassette 12 during the presentimage capturing process, or amounts of electric power consumed by theradiation source device 18 and the cassette 12 in the previous imagecapturing process. If a re-supply instruction is input from there-supply instructing unit 382, then theamount-of-consumed-electric-power predictor 414 calculates amounts ofelectric power to be consumed by the respective devices indicated by theIDs, i.e., the radiation source device 18 and the cassette 12 to bere-supplied with electric power, from image capturing conditions for theimage capturing process to be carried out, from which image capturingconditions for radiographic images already captured (indicated by thecount) are excluded, which are among the present image capturingconditions representative of the number of radiographic images to becaptured, mAs values, etc., and corrects the calculated amounts ofelectric power by multiplying the calculated amounts by usage historiesof the radiation source device 18 and the cassette 12, i.e.,coefficients corresponding to the number of times that the radiationsource device 18 and the cassette 12 have been used, thereby predictingamounts of electric power that will be consumed by the devices of theIDs in the image capturing process to be carried out.

The information updater 416 subtracts the amount of supplied electricpower from the remaining level of electric power of a device serving asan electric power supply source, and adds the amount of suppliedelectric power to the remaining level of electric power of a device thatserves as an electric power supply destination, in the remaininglevel-of-electric-energy information table. If the re-supply instructingunit 382 outputs a re-supply instruction, then the information updater416 changes only the remaining levels of electric power of therespective devices indicated by the IDs. A value produced by adding thepresent amount of supplied electric power to the amount of electricpower included in the re-supply instruction signal is recorded in thememory 330. Since this value reflects the amount of electric power fromthe electric power supply controller 374, an error in the remaininglevel of electric power, which is represented by only a predicted value,is corrected.

According to the second specific example, because the electric powercontroller 334 includes the electric power manager 390, the electricpower supply route setting unit 370 and theamount-of-supplied-electric-power setting unit 372 operate differentlyfrom those of the electric power controller 334 according to the firstspecific example.

More specifically, the electric power supply route setting unit 370according to the second specific example sets a route for supply ofelectric power based on the predicted amount of electric power, and theremaining levels of electric power in the batteries 308 of the radiationsource device 18 and the cassette 12 (remaining level-of-electric-energyinformation tables). Typically, the electric power supply route settingunit 370 sets a route for supplying electric power to a device, thebattery of which stores a remaining level of electric power that willalmost be eliminated in the present image capturing process. Informationconcerning the set route is displayed on the display screen of themobile terminal 42. If the re-supply instructing unit 382 outputs are-supply instruction, then the electric power supply route setting unit370 sets routes for supplying electric power to respective devicesindicated by the IDs. If the operator 38 intends to supply electricpower additionally from other devices, i.e., a radiation source device18 and a cassette 12 that are not used to capture radiographic images,then the operator 38 enters routes for supplying electric power, andamounts of electric power, from the other devices, i.e., routes forsupplying electric power from the other devices to the respectivedevices indicated by the IDs. If the operator 38 additionally intends tocharge a battery using another device, i.e., a radiation source device18 or a cassette 12, then the operator 38 enters a route for supplyingelectric power to or from the other device, i.e., a route from the otherdevice to the radiation source device 18 or the cassette 12 that is usedto capture radiographic images, or a route from the radiation sourcedevice 18 or the cassette 12 that is used to capture radiographic imagesto the other device, together with the amount of electric power to besupplied, and an order in which such electric power is supplied. Basedon the entered route for supplying electric power, the electric powersupply route setting unit 370 outputs a supply source instruction signalor a supply destination instruction signal to the electric power supplycontroller 374 of each of the devices.

The amount-of-supplied-electric-power setting unit 372 according to thesecond specific example sets the supplied amount of electric power basedon the predicted amount of electric power and the remaining levels ofelectric power in the batteries 308 of the radiation source device 18and the cassette 12 (remaining level-of-electric-energy informationtables). Thus, at most, the predicted amount of electric power issupplied to a device, the battery of which stores a remaining level ofelectric power, which will almost be eliminated during the present imagecapturing process. The amount of electric power, which is supplied tosuch a device, may be one-half or one-third the predicted amount ofelectric power. The information concerning the set amount of electricpower is displayed on a display screen of the mobile terminal 42. Theset amount of electric power can also be changed as desired by themobile terminal 42. If the operator 38 additionally intends to charge abattery, then the amount-of-supplied-electric-power setting unit 372also sets the amount of electric power to be supplied, so as toadditionally charge the battery. The amount of electric power predictedbased on previous image capturing conditions is supplied in order tosupplement the amount of electric power consumed in the previous imagecapturing process. If the re-supply instructing unit 382 outputs are-supply instruction, then the amount-of-supplied-electric-powersetting unit 372 sets the amount of electric power to equal thepredicted amount of electric power. The set amount of electric power canbe changed as desired by the mobile terminal 42. If the operator 38additionally intends to charge a battery, then theamount-of-supplied-electric-power setting unit 372 also sets an amountof electric power to be supplied, so as to additionally charge thebattery. The set amount of electric power then is supplied to theelectric power supply controller 374 of the corresponding device.

Among functional components that are ancillary to the electric powermanager 390, the remaining level prediction updater 392 shown in FIG. 22functions, assuming that the supply timing conditions recorded in thememory 330 indicate supply of electric power before capturing ofradiographic images. Each time that the operator 38 turns on theexposure switch 48, the remaining level prediction updater 392 updates,by way of subtraction, the remaining levels of electric power stored inthe batteries that are recorded in the remaininglevel-of-electric-energy information tables, i.e., the remaining levelsof electric power stored in the batteries 308 of the radiation sourcedevice 18 and the cassette 12, which are used to capture radiographicimages. More specifically, with respect to the radiation source device18 and the cassette 12, the remaining level prediction updater 392calculates amounts of electric power consumed in order to captureradiographic images based on the image capturing conditions and theusage history tables, and subtracts the calculated amounts of electricpower from the remaining levels of electric power stored in thebatteries 308 of the radiation source device 18 and the cassette 12,which are recorded in the remaining level-of-electric-energy informationtables.

The usage history updater 394 adds to the usage counts recorded in theusage history tables the number of times that the exposure switch 48 hasbeen turned on, i.e., the number of times that the radiation sourcedevice 18 and the cassette 12 have been used.

If the supply timing conditions recorded in the memory 330 indicatesupply of electric power before capturing of radiographic images, thenthe remaining level information transfer unit 396 shown in FIG. 22transfers the remaining level-of-electric-energy information tables viathe network to the database of a data center, such as a medicalorganization or the like for updating, based on an image capturecompletion signal input from the image capture completion determiner386. If the supply timing conditions recorded in the memory 330 indicatesupply of electric power after capturing of radiographic images, thenthe remaining level information transfer unit 396 transfers theremaining level-of-electric-energy information tables via the network tothe database of the data center for updating, based on an electric powersupply completion signal input from the electric power supply completionoutput unit 388.

If the supply timing conditions recorded in the memory 330 indicatesupply of electric power before capturing of radiographic images, thenthe usage history transfer unit 398 transfers the usage history tablesvia the network to the database of the data center for updating, basedon an image capture completion signal input from the image capturecompletion determiner 386. If the supply timing conditions recorded inthe memory 330 indicate supply of electric power after capturing ofradiographic images, then the usage history transfer unit 398 transfersthe usage history tables via the network to the database of the datacenter for updating, based on an electric power supply completion signalinput from the electric power supply completion output unit 388.

The first mobile apparatus 1000A basically is constructed as describedabove. Operations of the first mobile apparatus 1000A will be describedbelow with reference to the flowcharts shown in FIGS. 26 through 32.

First, an operation sequence of the first mobile apparatus 1000A, if thesupply timing conditions are free of timing controls, will be describedbelow with reference to the flowcharts shown in FIGS. 26 and 27.

The operator 38 moves the cart unit 1002 toward a subject 50 whoseradiographic images are to be captured. Then, the operator 38 takes outthe first radiographic apparatus 10A from the cart unit 1002, andseparates the radiation source device 18 from the cassette 12.Thereafter, the radiation source device 18 is attached to the distal end1006 a of the arm unit 1006. If recumbent image capturing is to becarried out, for example, the cassette 12 is disposed between thesubject 50 and a bed 1040 or a sheet (blanket etc.). Then, the operator38 turns on an electric power supply switch (ON operation). The ONoperation of the electric power supply switch includes the clicking ofthe left button of a mouse on an icon representing an electric powersupply switch shown on the display unit 1010 of the console 1004.Alternatively, the ON operation may be performed using an operationswitch on the cart unit 1002 that is dedicated for electric power supplyoperation.

In step S1, the electric power controller 334 is activated based onoperation of the electric power supply switch. The electric power supplyactivator 336 may also activate the electric power controller 334 by asupply instruction of electric power from another communication device,without operation of the electric power supply switch by the operator38. In this case, the electric power supply activator 336 of each of thedevices refers to interlock information registered in the memory 330,i.e., an ID of the radiation source device 18 or the cassette 12 that isused in a predesignated image capturing process, and only the electricpower supply activator 336 of the device having an ID is identical tothat of the interlock information activates the corresponding electricpower controller 334.

In step S2, the device connection detector 360 detects whether or notthe device, i.e., the radiation source device 18 or the cassette 12, isconnected to the first energy input/output unit 300 or to the secondenergy input/output unit 302.

After the device connection detector 360 has detected the connection instep S2, the cassette selector activator 362 determines whether or notconditions are satisfied for activating the cassette selector 364 instep S3. More specifically, the cassette selector activator 362activates the cassette selector 364 if a condition concerning a route,from among the battery charging conditions stored in the memory 330,represents only supply of electric power from one cassette 12 to theradiation source device 18, the aforesaid device is the radiation sourcedevice 18, and connection of a plurality of cassettes 12 to theradiation source device 18 is detected.

In step S4, the cassette selector 364 selects a cassette 12 that matchesthe selecting conditions from among the connected cassettes 12, based ona plurality of IDs that are acquired by the cassette ID acquirer 400,selecting conditions stored in the memory 330, and the cassetteinformation tables and the usage history tables, which are acquired bythe cassette information acquirer 402. The cassette selector 364 thenoutputs the ID of the selected cassette 12 to the electric power supplyroute setting unit 370.

After step S4, or if the cassette selector activator 362 judges thatconditions are not satisfied for activating the cassette selector 364 instep S3, control proceeds to step S5, during which the integrated supplyactivator 366 determines whether conditions are not satisfied in orderto activate the integrated supply 368. More specifically, the integratedsupply activator 366 activates the integrated supply 368 if a conditionconcerning a route, from among the battery charging conditions stored inthe memory 330, represents only supply of electric power from aplurality of cassettes 12 to the radiation source device 18, theaforesaid device is the radiation source device 18, and connection of aplurality of cassettes 12 to the radiation source device 18 is detected.

In step S6, the integrated supply 368 sets weighting coefficients forthe amounts of electric power to be supplied from the cassettes 12 tothe radiation source device 18 based on a plurality of IDs that areacquired by the cassette ID acquirer 400, integrating conditions storedin the memory 330, the cassette information tables, and the usagehistory tables, which are acquired by the cassette information acquirer402. The integrated supply 368 then outputs the set weightingcoefficients to the corresponding amount-of-supplied-electric-powersetting unit 372.

After step S6, or if the integrated supply activator 366 judges thatconditions are not satisfied for activating the integrated supply 368 instep S5, then control proceeds to step S7, during which the electricpower supply route setting unit 370 sets a route for supply of electricpower, based on conditions concerning the route from among the batterycharging conditions stored in the memory 330. For example, the electricpower supply route setting unit 370 sets a route from the radiationsource device 18 to the cassette 12, or a route from the cassette 12 tothe radiation source device 18. If the electric power supply routesetting unit 370 is supplied with an ID from the cassette selector 364,then the electric power supply route setting unit 370 sets a route fromthe cassette 12 identified by the ID to the radiation source device 18.If the electric power supply route setting unit 370 is supplied with aplurality of IDs from the integrated supply 368, then the electric powersupply route setting unit 370 sets multiple routes from the cassettes 12identified by the IDs to the radiation source device 18. Thereafter, theelectric power supply route setting unit 370 outputs informationconcerning the set route (route information) to the electric powersupply controller 374. More specifically, based on the set route forsupply of electric power, the electric power supply route setting unit370 outputs a supply source instruction signal, or a supply destinationinstruction signal, to the electric power supply controller 374 of eachdevice. For example, it is assumed that the first energy input/outputunit 300 of the radiation source device 18 is connected to the firstenergy input/output unit 300 of the cassette 12. If the set route is aroute for supplying electric power from the radiation source device 18to the cassette 12, then the electric power supply route setting unit370 outputs a supply source instruction signal to the electric powersupply controller 374 of the radiation source device 18, and furtheroutputs a supply destination instruction signal to the electric powersupply controller 374 of the cassette 12. If the set route is a routefor supplying electric power from the cassette 12 to the radiationsource device 18, then the electric power supply route setting unit 370outputs a supply destination instruction signal to the electric powersupply controller 374 of the radiation source device 18, and furtheroutputs a supply source instruction signal to the electric power supplycontroller 374 of the cassette 12.

In step S8, the amount-of-supplied-electric-power setting unit 372 setsan amount of electric power to be supplied (supplied amount of electricpower) based on a condition concerning the amount of electric power tobe supplied, from among the battery charging conditions. For example,the amount-of-supplied-electric-power setting unit 372 sets an amount ofelectric power to be supplied for a full battery charge, or forcapturing a single radiographic image. If theamount-of-supplied-electric-power setting unit 372 is supplied with aplurality of IDs and corresponding coefficients from the integratedsupply 368, then the amount-of-supplied-electric-power setting unit 372multiplies the amount of electric power to be supplied by suchcoefficients in order to set respective amounts of electric power to besupplied to the radiation source device 18 from the respective cassettes12. The amount-of-supplied-electric-power setting unit 372 outputsinformation concerning the set amounts of electric power to be suppliedto the electric power supply controllers 374 of the correspondingdevices.

In step S9, if the electric power supply controller 374 is supplied witha supply source instruction signal, then the electric power supplycontroller 374 controls the battery 308 in order to output electricpower. Further, if the electric power supply controller 374 is suppliedwith a supply destination instruction signal, then the electric powersupply controller 374 controls the battery 308 so as to be supplied withelectric power. In a case where supply of electric power to the battery308 or supply of electric power from the battery 308 is completed, thenthe electric power supply controller 374 outputs a supply terminationsignal.

In step S10, the electric power supply completion output unit 388outputs an electric power supply completion signal based on supplytermination signals, which are input from the electric power supplycontrollers 374 of all of the devices to which electric power has beensupplied.

In step S11, the image capture permission instructing unit 384 outputs amessage representative of permission to capture an image to the console1004 and the mobile terminal 42, based on the electric power supplycompletion signal input from the electric power supply completion outputunit 388.

In step S12, the operator 38 prepares the first mobile apparatus 1000Afor capturing radiographic images at a site where the first mobileapparatus 1000A has been carried. This preparatory procedure has beendescribed in detail above, and will not be described below.

If the subject 50 is positioned during the preparatory procedure,control proceeds to step S13 shown in FIG. 27, in which the operator 38turns on the exposure switch 48 to begin capturing radiographic imagesof the subject 50. In this case, the counter 380 updates the count byincrementing the count by +1.

When the operator 38 turns on the exposure switch 48 in step S13, thenin step S14, the electric power supply limiter 338 outputs a supplylimit signal to the electric power controller 334 during theaforementioned period. During the period in which the electric powercontroller 334 is supplied with the supply limit signal, the electricpower controller 334 temporarily interrupts the operation thereof tosupply electric power.

In step S15, the electric power controller 334 determines whether or notelectric power needs to be re-supplied, based on whether the electricpower supply controller 374 of any device has output an imaging disabledsignal. More specifically, if the remaining level of electric powerstored in the battery 308 of the radiation source device 18 or thecassette 12 is insufficient to capture a single radiographic image, thenthe electric power supply controller 374 outputs an imaging disabledsignal, including the remaining level of electric power and the ID ofthe aforesaid device to the re-supply instructing unit 382, for therebyrequesting the re-supply instructing unit 382 to re-supply electricpower.

If the electric power controller 334 judges that electric power needs tobe re-supplied, then control proceeds to step S16, in which the imagecapture interruption instructing unit 378 outputs a message indicatinginterruption of image capturing to the console 1004 and the mobileterminal 42. The console 1004 and the mobile terminal 42 display amessage on the display unit 1010 and a display screen thereof,respectively, and preferably output an alarm sound, for prompting theoperator 38 to interrupt the image capturing process.

Thereafter, in step S17, the re-supply instructing unit 382 outputs are-supply instruction signal to the electric power supply route settingunit 370, as well as to the amount-of-supplied-electric-power settingunit 372.

In step S18, the electric power supply route setting unit 370 sets aroute for re-supplying electric power (re-supply route) based on thebattery charging conditions, and based on the set re-supply route,outputs a supply source instruction signal or a supply destinationinstruction signal to the electric power supply controller 374 of eachdevice.

In step S19, the amount-of-supplied-electric-power setting unit 372 setsan amount of electric power to be re-supplied (amount of re-suppliedelectric power) based on a condition concerning the supplied amount,from among the battery charging conditions, and outputs informationconcerning the set amount of re-supplied electric power to the electricpower supply controller 374 of the corresponding device.

In step S20, if the electric power supply controller 374 is suppliedwith a supply source instruction signal, then the electric power supplycontroller 374 controls the battery 308 in order to output electricpower. Further, if the electric power supply controller 374 is suppliedwith a supply destination instruction signal, then the electric powersupply controller 374 controls the battery 308 so as to be supplied withelectric power. In a case where supply of electric power to the battery308, or supply of electric power from the battery 308 is completed, theelectric power supply controller 374 outputs a supply terminationsignal.

In step S21, the electric power supply completion output unit 388outputs an electric power supply completion signal, based on supplytermination signals that are input from the electric power supplycontrollers 374 of all of the devices to which electric power isre-supplied.

In step S22, the image capture permission instructing unit 384 outputs amessage representing permission to capture an image to the mobileterminal 42, based on the electric power supply completion signal inputfrom the electric power supply completion output unit 388. Thereafter,control returns to step S13 shown in FIG. 27 and steps subsequentthereto.

If the electric power controller 334 judges that no electric power needsto be re-supplied in step S15, then control proceeds to step S23, inwhich the image capture completion determiner 386 determines whether ornot the image capturing process is completed, by comparing the number oftimes that radiographic images have been captured in the image capturingconditions with the count from the counter 380. If the count is smallerthan the number of times that radiographic images have been captured,then control returns to step S13 shown in FIG. 27, and step S13 andsteps subsequent thereto are repeated until the image capturing processis brought to an end. If the image capturing process is completed,control proceeds to step S24, in which the electric power controller 334is temporarily shut down. More specifically, the image capturecompletion determiner 386 outputs an image capture completion signal.Based on the image capture completion signal input from the imagecapture completion determiner 386, the pause processor 340 outputs apause signal to the electric power controller 334. Based on the pausesignal input from the pause processor 340, the electric power controller334 stops controlling supply of electric power, and waits to beactivated at a subsequent time by the electric power supply activator336. At this stage, the operation sequence of the first radiographicapparatus 10A is brought to an end. If the electric power supply switchis operated again or the electric power supply is turned on again, stepS1 shown in FIG. 26 and steps subsequent thereto are repeated.

An operation sequence of the first radiographic apparatus 10A, if thesupply timing conditions indicate supply of electric power beforecapturing of radiographic images, will be described below with referenceto the flowcharts shown in FIGS. 28 through 30. Although the electricpower manager 390 mainly is involved in the operation sequence to bedescribed below, the cassette selector 364 and the integrated supply 368may also be included in the operation sequence.

In step S101 shown in FIG. 28, a message is output to the console 1004and the mobile terminal 42 for prompting the operator 38 to enter imagecapturing conditions.

In step S102, the electric power supply activator 336 activates theelectric power controller 334 based on the present image capturingconditions (order) entered from the console 1004 or the mobile terminal42. In this case, only the electric power supply activator 336 of adevice having an ID, which is the same as the ID of the radiation sourcedevice 18 or the cassette 12 used to capture radiation images, which hasbeen registered in advance in the image capturing conditions, activatesthe corresponding electric power controller 334. The present imagecapturing conditions may be input from the data center via the networkand the mobile terminal 42. The present image capturing conditions arestored in the memory 330.

In step S103, the device connection detector 360 detects whether or notthe device, i.e., the radiation source device 18 or the cassette 12, isconnected to the first energy input/output unit 300 or the second energyinput/output unit 302. After the device connection detector 360 hasdetected the connection in step S103, control proceeds to step S104, inwhich the ID acquirer 410 of the electric power manager 390 shown inFIG. 25 acquires the ID of the connected device. More specifically, theID acquirer 410 sends a transfer request requesting the connected deviceto transfer the ID thereof. The connected device outputs the ID to theelectric power manager 390, and the ID acquirer 410 acquires the ID andstores the ID in the memory 330.

In step S105, the information acquirer 412 for acquiring variousinformation acquires the present image capturing conditions, whichalready have been stored in the memory 330, a remaininglevel-of-electric-energy information table corresponding to the ID,previous image capturing conditions corresponding to the ID, and a usagehistory table corresponding to the ID, and stores such information inthe memory 330.

In step S106, the amount-of-consumed-electric-power predictor 414calculates amounts of electric power to be consumed by the radiationsource device 18 and the cassette 12 that is used to captureradiographic images, from conditions concerning the amount of electricpower to be supplied (stored in the memory 330), and the present orprevious image capturing conditions, which represent the number ofradiographic images to be captured, mAs values, etc., from among thebattery charging conditions. The amount-of-consumed-electric-powerpredictor 414 then corrects the calculated amounts of electric power bymultiplying the calculated amounts by usage histories of the radiationsource device 18 and the cassette 12, i.e., by coefficientscorresponding to the number of times that the radiation source device 18and the cassette 12 have been used, thereby predicting amounts ofelectric power that are consumed by the radiation source device 18 andthe cassette 12 during the present image capturing process, or amountsof electric power consumed by the radiation source device 18 and thecassette 12 during the previous image capturing process. The conditionconcerning amount of electric power from among the battery chargingconditions may be an amount of electric power required to captureradiographic images in the present image capturing process, an amount ofelectric power required to capture a single radiographic image, or anamount of electric power consumed during the previous image capturingprocess. If the condition concerning the amount of electric power is anamount of electric power required to capture radiographic images duringthe present image capturing process, then theamount-of-consumed-electric-power predictor 414 calculates amounts ofelectric power that are consumed by the radiation source device 18 andthe cassette 12 used to capture radiographic images in the present imagecapturing process, and corrects the calculated amounts of electric powerby multiplying the calculated amounts by usage histories of theradiation source device 18 and the cassette 12, i.e., by coefficientscorresponding to the number of times that the radiation source device 18and the cassette 12 have been used, thereby predicting amounts ofelectric power that are consumed by the radiation source device 18 andthe cassette 12 during the present image capturing process, or amountsof electric power consumed by the radiation source device 18 and thecassette 12 during the previous image capturing process. If thecondition concerning amount of electric power is an amount of electricpower consumed during the previous image capturing process, then theamount-of-consumed-electric-power predictor 414 calculates amounts ofelectric power consumed by the radiation source device 18 and thecassette 12 in the previous image capturing process, and corrects thecalculated amounts of electric power by multiplying the calculatedamounts by usage histories of the radiation source device 18 and thecassette 12, i.e., by coefficients corresponding to the number of timesthat the radiation source device 18 and the cassette 12 have been used,thereby predicting amounts of electric power consumed by the radiationsource device 18 and the cassette 12 during the previous image capturingprocess.

In step S107, the electric power supply route setting unit 370 sets aroute for supply of electric power based on the predicted amounts ofelectric power, and the remaining levels of electric power in thebatteries 308 of the radiation source device 18 and the cassette 12(remaining level-of-electric-energy information tables). Typically, theelectric power supply route setting unit 370 sets a route for supply ofelectric power to a device, the battery of which stores a remaininglevel of electric power that will be almost eliminated during thepresent image capturing process. Information concerning the set route isdisplayed on the display screen of the mobile terminal 42. If theoperator 38 intends to supply electric power additionally from otherdevices, i.e., a radiation source device 18 or a cassette 12 that arenot used to capture radiographic images, then the operator 38 entersroutes for supplying electric power from such other devices, i.e.,routes for supplying electric power from the other devices to thedevices having IDs, together with amounts of electric power. If theoperator 38 intends to charge a battery as well using another device,i.e., a radiation source device 18 or a cassette 12, then the operator38 enters a route for supplying electric power to or from the otherdevice, i.e., a route from the other device to the radiation sourcedevice 18 or the cassette 12 that is used to capture radiographicimages, or a route from the radiation source device 18 or the cassette12 that is used to capture radiographic images to the other device,together with an amount of electric power to be supplied and the orderin which electric power is supplied. Based on the entered route forsupplying electric power, the electric power supply route setting unit370 outputs a supply source instruction signal or a supply destinationinstruction signal to the electric power supply controller 374 of eachof such devices.

In step S108, the amount-of-supplied-electric-power setting unit 372sets an amount of electric power to be supplied (supplied amount ofelectric power) based on the predicted amount of electric power and theremaining levels of electric power in the batteries 308 of the radiationsource device 18 and the cassette 12 (remaining level-of-electric-energyinformation tables). Thus, at most, the predicted amount of electricpower is supplied to a device, the battery of which stores a remaininglevel of electric power that will be almost eliminated during thepresent image capturing process. The amount of electric power, which issupplied to such a device, may be one-half or one-third the predictedamount of electric power. The information of the set amount of electricpower is displayed on the display unit 1010 of the console 1004 and adisplay screen of the mobile terminal 42. The set amount of electricpower also can be changed as desired by the console 1004 and the mobileterminal 42. If the operator 38 intends to charge a battery as well,then the amount-of-supplied-electric-power setting unit 372 also sets anamount of electric power to be supplied additionally to charge thebattery. The amount of electric power, which is predicted based on theprevious image capturing conditions, is supplied in order to supplementthe amount of electric power consumed during the previous imagecapturing process. If the operator 38 intends to charge a battery aswell, then the amount-of-supplied-electric-power setting unit 372 alsosets an amount of electric power to be supplied additionally to chargethe battery. The set amount of electric power is supplied to theelectric power supply controller 374 of the corresponding device.

In step S109, if the electric power supply controller 374 is suppliedwith a supply source instruction signal, then the electric power supplycontroller 374 controls the battery 308 to output electric power. If theelectric power supply controller 374 is supplied with a supplydestination instruction signal, then the electric power supplycontroller 374 controls the battery 308 so as to be supplied withelectric power. If supply of electric power to the battery 308 or supplyof electric power from the battery 308 is completed, the electric powersupply controller 374 outputs a supply termination signal.

In step S110, the information updater 416 of the electric power manager390, in the remaining level-of-electric-energy information table,subtracts the amount of supplied electric power from the remaining levelof electric power of the device that serves as the electric power supplysource, and adds the amount of supplied electric power to the remaininglevel of electric power of the device that serves as the electric powersupply destination.

In step S111, the electric power supply completion output unit 388outputs an electric power supply completion signal based on supplytermination signals input from the electric power supply controllers 374of all of the devices to which electric power has been supplied.

In step S112, the image capture permission instructing unit 384 outputsa message, which represents permission to capture an image, to themobile terminal 42 based on the electric power supply completion signalinput from the electric power supply completion output unit 388.

In step S113 shown in FIG. 29, the operator 38 prepares the firstradiographic apparatus 10A for capturing radiographic images, at a siteto which the first radiographic apparatus 10A has been carried. Thispreparatory procedure has already been described in detail above, andwill not be described below.

In step S114, the operator 38 turns on the exposure switch 48 in orderto start capturing radiographic images of the subject 50. In this case,the counter 380 updates the count thereof by incrementing the count by+1.

When the operator 38 turns on the exposure switch 48 in step S114, theelectric power supply limiter 338 outputs a supply limit signal to theelectric power controller 334, during the period referred to above instep S115. During the period in which the electric power controller 334is supplied with the supply limit signal, the electric power supplyoperation of the electric power controller 334 is limited.

In step S116, the remaining level prediction updater 392 updates, by wayof subtraction, the remaining levels of electric power stored in thebatteries, which are recorded in the remaining level-of-electric-energyinformation tables, i.e., the remaining levels of electric power storedin the batteries 308 of the radiation source device 18 and the cassette12, which are utilized for capturing radiographic images. Morespecifically, with respect to the radiation source device 18 and thecassette 12 that carry out capturing of radiographic images, theremaining level prediction updater 392 calculates the amounts ofelectric power consumed during each time the exposure switch 48 isturned on, based on the image capturing conditions and the usage historytables, and subtracts the calculated amounts of electric power from theremaining levels of electric power stored in the batteries 308 of theradiation source device 18 and the cassette 12, which are recorded inthe remaining level-of-electric-energy information tables.

In step S117, the electric power controller 334 determines whether ornot electric power needs to be re-supplied, based on whether theelectric power supply controller 374 of any device has output an imagingdisabled signal.

If the electric power controller 334 judges that electric power needs tobe re-supplied, then control proceeds to step S118, in which the imagecapture interruption instructing unit 378 outputs a message indicativeof an image capture interruption to the console 1004 and the mobileterminal 42. The console 1004 and the mobile terminal 42 displays themessage on the display unit 1010 and a display screen thereof,respectively, and preferably output an alarm sound, for prompting theoperator 38 to interrupt the image capturing process.

Thereafter, in step S119, the re-supply instructing unit 382 outputs are-supply instruction signal to the electric power supply route settingunit 370, the amount-of-supplied-electric-power setting unit 372, andthe electric power manager 390.

In step S120, the electric power supply route setting unit 370 sets, asa re-supply route, a route for supplying electric power to the devicehaving the ID included in the input re-supply instruction signal, andoutputs a supply source instruction signal or a supply destinationinstruction signal to the electric power supply controller 374 of eachdevice, based on the set re-supply route.

In step S121, the amount-of-consumed-electric-power predictor 414calculates amounts of electric power to be consumed by the device havingthe aforementioned ID, i.e., the radiation source device 18 or thecassette 12 that is re-supplied with electric power, from among theimage capturing conditions for an image capturing process to be carriedout, and from which image capturing conditions for radiographic imagesalready captured (indicated by the count) are excluded, among thebattery charging conditions stored in the memory 330 and the presentimage capturing conditions representative of the number of radiographicimages to be captured, mAs values, etc. Theamount-of-consumed-electric-power predictor 414 also corrects thecalculated amounts of electric power by multiplying the calculatedamounts by the usage history of the device having the ID, i.e., acoefficient corresponding to the number of times that the device of theID has been used, thereby predicting an amount of electric power thatwill be consumed by the device of the ID in the image capturing processto be carried out.

In step S122, the amount-of-supplied-electric-power setting unit 372sets the amount of electric power predicted by theamount-of-consumed-electric-power predictor 414, as an amount ofre-supplied electric power, and supplies information concerning the setamount of re-supplied electric power to the electric power supplycontroller 374 of the corresponding device.

In step S123, if the electric power supply controller 374 is suppliedwith a supply source instruction signal, then the electric power supplycontroller 374 controls the battery 308 to output electric power. If theelectric power supply controller 374 is supplied with a supplydestination instruction signal, then the electric power supplycontroller 374 controls the battery 308 so as to be supplied withelectric power. If supply of electric power to the battery 308 or supplyof electric power from the battery 308 is completed, the electric powersupply controller 374 outputs a supply termination signal.

In step S124, the electric power supply completion output unit 388outputs an electric power supply completion signal, based on supplytermination signals input from the electric power supply controllers 374of all of the devices to which electric power has been re-supplied.

In step S125, the image capture permission instructing unit 384 outputsa message to the console 1004 and the mobile terminal 42 representingpermission to capture images, based on the electric power supplycompletion signal input from the electric power supply completion outputunit 388. Thereafter, control returns to step S114 and steps subsequentthereto.

If the electric power controller 334 judges that no electric power needsto be re-supplied in step S117, then control proceeds to step S126 shownin FIG. 30, in which the image capture completion determiner 386determines whether or not the image capturing process is completed bycomparing the number of times that radiographic images have beencaptured in the image capturing conditions with the count of the counter380. If the count is smaller than the number of times that radiographicimages have been captured, then control returns to step S114 shown inFIG. 29, and step S114 and steps subsequent thereto are repeated untilthe image capturing process is brought to an end. If the image capturingprocess is completed, control proceeds to step S127 shown in FIG. 30, inwhich the usage history updater 394 adds the number of times that theexposure switch 48 has been turned on to the number of times recorded inthe usage history table, i.e., the number of times that the radiationsource device 18 and the cassette 12 have been used to captureradiographic images.

In step S128, the remaining level information transfer unit 396transfers the remaining level information table via the network to thedatabase of the data center for updating.

In step S129, the usage history transfer unit 398 transfers the usagehistory table via the network to the database of the data center forupdating.

In step S130, the electric power controller 334 is temporarily shutdown. More specifically, the image capture completion determiner 386outputs an image capture completion signal. Based on the image capturecompletion signal input from the image capture completion determiner386, the pause processor 340 outputs a pause signal to the electricpower controller 334. Based on the pause signal input from the pauseprocessor 340, the electric power controller 334 stops controllingsupply of electric power, and waits to be activated at a subsequent timeby the electric power supply activator 336. At this stage, the operationsequence of the first radiographic apparatus 10A is brought to an end.If the image capturing conditions are entered again, then step S102shown in FIG. 28 and steps subsequent thereto are repeated.

An operation sequence of the first radiographic apparatus 10A, if thesupply timing conditions indicate supply of electric power aftercapturing of radiographic images, will be described below with referenceto the flowcharts shown in FIGS. 31 and 32. Although the electric powermanager 390 mainly is involved in the operation sequence to be describedbelow, the cassette selector 364 and the integrated supply 368 may alsobe included in the operation sequence.

In step S201 shown in FIG. 31, a message is output to the console 1004and the mobile terminal 42, for prompting the operator 38 to enter imagecapturing conditions.

In step S202, the operator 38 prepares the first radiographic apparatus10A for capturing radiographic images at a site where the firstradiographic apparatus 10A has been carried. In step S203, the operator38 turns on the exposure switch 48 to start capturing radiographicimages of the subject 50.

In step S204, the electric power controller 334 determines whether ornot electric power needs to be re-supplied, based on whether theelectric power supply controller 374 of any given device has output animaging disabled signal.

If the electric power controller 334 judges that electric power needs tobe re-supplied, then control proceeds to step S205, in which the imagecapture interruption instructing unit 378 outputs a message indicatinginterruption of image capturing to the console 1004 and the mobileterminal 42. Thereafter, in step S206, the re-supply instructing unit382 outputs a re-supply instruction signal to the electric power supplyroute setting unit 370, the amount-of-supplied-electric-power settingunit 372, and the electric power manager 390, thereby activating theelectric power supply route setting unit 370, theamount-of-supplied-electric-power setting unit 372, and the electricpower manager 390 in an interrupt routine.

In step S207, the electric power supply route setting unit 370 sets aroute for supplying electric power to the device having the ID includedin the input re-supply instruction signal, as a re-supply route, andbased on the set re-supply route, outputs a supply source instructionsignal or a supply destination instruction signal to the electric powersupply controller 374 of each device.

In step S208, the amount-of-consumed-electric-power predictor 414calculates amounts of electric power that are consumed by the devicehaving the ID, i.e., the radiation source device 18 or the cassette 12that are re-supplied with electric power, from image capturingconditions for an image capturing process to be carried out, from whichimage capturing conditions for radiographic images already captured(indicated by the count) are excluded, from among the battery chargingconditions stored in the memory 330, and the present image capturingconditions representative of the number of radiographic images to becaptured, mAs values, etc. The amount-of-consumed-electric-powerpredictor 414 also corrects the calculated amounts of electric power bymultiplying the calculated amounts by a usage history of the device ofthe ID, i.e., a coefficient corresponding to the number of times thatthe device of the ID has been used, thereby predicting an amount ofelectric power to be consumed by the device of the ID in the imagecapturing process to be carried out.

In step S209, the amount-of-supplied-electric-power setting unit 372sets the amount of electric power predicted by theamount-of-consumed-electric-power predictor 414 as an amount ofre-supplied electric power, and outputs the information concerning theset amount of re-supplied electric power to the electric power supplycontroller 374 of the corresponding device.

In step S210, if the electric power supply controller 374 is suppliedwith a supply source instruction signal, then the electric power supplycontroller 374 controls the battery 308 to output electric power.Further, if the electric power supply controller 374 is supplied with asupply destination instruction signal, then the electric power supplycontroller 374 controls the battery 308 so as to be supplied withelectric power. If supply of electric power to the battery 308 or supplyof electric power from the battery 308 is completed, then the electricpower supply controller 374 outputs a supply termination signal.

In step S211, the electric power supply completion output unit 388outputs an electric power supply completion signal based on supplytermination signals, which are input from the electric power supplycontrollers 374 of all of the devices to which electric power has beenre-supplied.

In step S212, the image capture permission instructing unit 384 outputsa message representing permission to capture an image to the console1004 and the mobile terminal 42, based on the electric power supplycompletion signal input from the electric power supply completion outputunit 388. Thereafter, control returns to step S203 and steps subsequentthereto.

If the electric power controller 334 judges that no electric power needsto be re-supplied in step S204, then control proceeds to step S213, inwhich the image capture completion determiner 386 determines whether ornot the image capturing process is completed. If the image capturingprocess is not completed, then control returns to step S203, and stepS203 and steps subsequent thereto are repeated until the image capturingprocess is brought to an end. If the image capturing process hasfinished, control proceeds to step S214, in which the electric powersupply activator 336 activates the electric power controller 334 basedon an image capture completion signal input from the image capturecompletion determiner 386. In this case, only the electric power supplyactivator 336 of a device having an ID that is the same as the ID of theradiation source device 18 or the cassette 12 that is used to captureradiation images, which has been registered in advance in the imagecapturing conditions, activates the corresponding electric powercontroller 334.

In step S215 shown in FIG. 32, the device connection detector 360detects whether or not the device is connected to the first energyinput/output unit 300 or the second energy input/output unit 302.

After the device connection detector 360 has detected the connection instep S215, control proceeds to step S216, in which the ID acquirer 410of the electric power manager 390 acquires the ID of the connecteddevice. Thereafter, in step S217, the information acquirer 412 foracquiring various information acquires the present image capturingconditions, which have already been stored in the memory 330, aremaining level-of-electric-energy information table corresponding tothe ID, previous image capturing conditions corresponding to the ID, anda usage history table corresponding to the ID, and stores suchinformation in the memory 330.

In step S218, the amount-of-consumed-electric-power predictor 414calculates amounts of electric power to be consumed by the radiationsource device 18 and the cassette 12, which are used to captureradiographic images, from a condition concerning the amount of electricpower to be supplied, and the present or previous image capturingconditions representative of the number of radiographic images to becaptured, mAs values, etc., from among the battery charging conditions.

In step S219, the electric power supply route setting unit 370 sets aroute for supply of electric power, based on the predicted amounts ofelectric power and the remaining levels of electric power in thebatteries 308 of the radiation source device 18 and the cassette 12(remaining level-of-electric-energy information tables).

Thereafter, in step S220, the amount-of-supplied-electric-power settingunit 372 sets an amount of electric power to be supplied (suppliedamount of electric power), based on the predicted amount of electricpower, and the remaining levels of electric power in the batteries 308of the radiation source device 18 and the cassette 12 (remaininglevel-of-electric-energy information tables).

In step S221, if the electric power supply controller 374 is suppliedwith a supply source instruction signal, then the electric power supplycontroller 374 controls the battery 308 to output electric power.Further, if the electric power supply controller 374 is supplied with asupply destination instruction signal, then the electric power supplycontroller 374 controls the battery 308 so as to be supplied withelectric power. In a case where supply of electric power to the battery308 or supply of electric power from the battery 308 is completed, theelectric power supply controller 374 outputs a supply terminationsignal.

In step S222, the information updater 416, in the remaininglevel-of-electric-energy information table, subtracts the amount ofsupplied electric power from the remaining level of electric power ofthe device that serves as an electric power supply source, and adds theamount of supplied electric power to the remaining level of electricpower of the device that serves as an electric power supply destination.

In step S223, the electric power supply completion output unit 388outputs an electric power supply completion signal, based on supplytermination signals input from the electric power supply controllers 374of all of the devices to which electric power has been supplied.

In step S224, the usage history updater 394 adds the number of timesthat the exposure switch 48 has been turned on to the number of timesrecorded in the usage history table, i.e., the number of times that theradiation source device 18 and the cassette 12 have been used to captureradiographic images.

In step S225, the remaining level information transfer unit 396transfers the remaining level information table via the network to thedatabase of the data center for updating. In step S226, the usagehistory transfer unit 398 transfers the usage history table via thenetwork to the database of the data center for updating. Thereafter, instep S227, the pause processor 340 temporarily shuts down the electricpower controller 334. At this stage, the operation sequence of the firstradiographic apparatus 10A is brought to an end. If the image capturingconditions are entered again, step S202 shown in FIG. 31 and stepssubsequent thereto are repeated.

For a method of supplying electric power using the console 1004,electric power may be supplied according to a process that differs fromthe process carried out by the above-mentioned process. For example, thedifferent process comprises an electric power collecting process forcollecting all or part of the electric power stored in the battery 308of the radiation source device 18, and all or part of the electric powerstored in the battery 308 of the cassette 12, for the battery unit 304of the console 1004.

An electric power collector 420 for carrying out the above electricpower collecting process will be described below with reference to FIGS.33 and 34.

The electric power collector 420 is incorporated in the batterycontroller 306. The electric power collector 420 is activated by anoperation made by the operator 38 in order to instruct collection ofelectric power, e.g., by left-clicking on an icon representingcollection of electric power shown on the display unit 1010 of theconsole 1004. As shown in FIG. 33, the electric power collector 420comprises the device connection detector 360, an electric powercollection ID acquirer 422, an electric power collection informationacquirer 424, an electric power collection supply route setting unit426, an electric power collection level setting unit 428, the electricpower supply controller 374, the remaining level detector 376, anelectric power collection remaining level updater 430, and an electricpower collection remaining level information transfer unit 432.

Details of an operation sequence of the electric power collector 420will be described below with reference to FIGS. 33 and 34.

In step S301 shown in FIG. 34, the device connection detector 360detects devices, i.e., the radiation source device 18 and the cassette12, which are connected to the first energy input/output unit 300 andthe second energy input/output unit 302.

The electric power collection ID acquirer 422 sends a transfer requestto the connected devices for transferring IDs. Based on the transferrequest, the connected devices output IDs thereof to the electric powercollector 420. The electric power collection ID acquirer 422 acquiresthe IDs from the connected devices, and registers the IDs in the memory330 (see FIG. 20) in step S302.

The electric power collection information acquirer 424 acquiresremaining level information tables corresponding to the IDs, and storesthe acquired remaining level information tables in the memory 330 instep S303.

The electric power collection supply route setting unit 426 sets asupply route from the device connected to the first energy input/outputunit 300 to the console 1004, and a supply route from the deviceconnected to the second energy input/output unit 302 to the console1004. Based on the set supply routes, in step S304, the electric powercollection supply route setting unit 426 outputs supply sourceinstruction signals to the electric power supply controllers 374 of therespective devices.

In step S305, the electric power collection level setting unit 428 setsan electric power collection level using the operating unit 1008, e.g.,a keyboard or a mouse, of the console 1004. The electric powercollection level represents the sum of a first electric power level tobe supplied from the device connected to the first energy input/outputunit 300 of the console 1004 to the battery 308 of the console 1004, anda second electric power level to be supplied from the device connectedto the second energy input/output unit 302 of the console 1004 to thebattery 308 of the console 1004. The first electric power level and thesecond electric power level are supplied respectively to the electricpower supply controllers 374 of the respective devices.

Based on the supply source instruction signals, the electric powersupply controllers 374 of the devices control the batteries 308 thereofto output electric power. Further, based on a supply source instructionsignal, the electric power supply controller 374 of the console 1004controls the battery 308 thereof to input electric power in step S306.The electric power supply controllers 374 control the batteries 308 tosupply electric power, and to be supplied with electric power, at aconstant charging rate or at a discharging rate based on the remaininglevel sent from the remaining level detector 376. If the level ofelectric power to be supplied is low, then it is possible to charge anddischarge the batteries 308 quickly.

In step S307, the electric power collection remaining level updater 430updates the remaining battery level corresponding to the ID of thedevice that is connected to the first energy input/output unit 300, bysubtracting the first electric power level from the remaining batterylevel. The electric power collection remaining level updater 430 alsoupdates the remaining battery level corresponding to the ID of thedevice that is connected to the second energy input/output unit 302, bysubtracting the second electric power level from the remaining batterylevel.

In a case where the updating process of the electric power collectionremaining level updater 430 is completed, then in step S308, theelectric power collection remaining level information transfer unit 432transfers the remaining level information tables via the network to thedatabase of the data center for updating.

The electric power collector 420 may be activated by operations made bythe operator 38 on the operating unit 1008, for example, regardless oflocation and time. For example, in a case where the first mobileapparatus 1000A is carried into a data center, the electric powercollector 420 may be activated in order to collect electric power in thebattery 308 of the console 1004. Then, in a case where the first mobileapparatus 1000A is carried to a site, the radiation source device 18 andthe cassette 12, which are used to capture radiographic images, may besupplied with electric power from the console 1004. In this case, theelectric power manager 390 supplies an optimum electric power level forcapturing radiographic images to the radiation source device 18 and tothe cassette 12. Alternatively, the electric power collector 420 may beactivated at a site, so as to collect into the console 1004 electricpower from a radiation source device 18 and a cassette 12, which havedeteriorated significantly and which cannot be used to captureradiographic images, and to supply the collected electric power to theradiation source device 18 and the cassette 12 that currently are beingused to capture radiographic images.

If the console 1004 is used, an electric power supply status (theremaining battery level) to the respective radiation source devices 18,and to the respective cassettes 12 in one or more first radiographicapparatus 10A may be displayed on the display unit 1010 of the console1004 as a guidance (mentioned as “guidance display”). Confirming theremaining battery level through the guidance display, the operator 38can easily determine which first radiographic apparatus 10A should beused, or which combination of the radiation source device 18 and thecassette 12 should be used. If such a guidance display as mentioned isused, the remaining level information from the respective remaininglevel detectors 376 or from the remaining level information table may beused.

Since the first mobile apparatus 1000A limits a route for supply ofelectric power, e.g., only the route from the radiation source device 18to the cassette 12, or only the route from the cassette 12 to theradiation source device 18. Thus, electric power does not have to besupplied in vain and the first mobile apparatus 1000A can reduceconsumption of electric power.

A battery is required for only the battery 308 of the radiation sourcedevice 18 or only the battery 308 of the cassette 12. For example, ifthe electric power controller 334 controls electric power supplied onlyalong a route from the radiation source device 18 to the cassette 12,then a built-in capacitor may be used as the battery 308 of the cassette12. In such a case, a separate battery is not required as the battery308 for the cassette 12. Similarly, if the electric power controller 334controls electric power so as to be supplied with power only along aroute from the cassette 12 to the radiation source device 18, then abuilt-in capacitor may be used as the battery 308 of the radiationsource device 18. In such a case, a separate battery is not required asthe battery 308 for the radiation source device 18.

Further, it is also possible to distinguish functions of a firstradiographic apparatus 10A having a built-in capacitor as the battery308 from those of a first radiographic apparatus 10A having a secondarybattery as the battery 308. A secondary battery utilizes chemicalreactions on positive and negative terminals, and can charge anddischarge. Though the capacity of a secondary battery is large, itcannot be charged quickly. On the other hand, a capacitor can be chargedquickly though the capacity thereof is not so large since electriccharge is stored using electrostatic force. Therefore, if the number ofradiographic images to be captured is large, then the first radiographicapparatus 10A having a secondary battery may be used. If a singleradiographic image is desired to be captured quickly, then the firstradiographic apparatus 10A having a built-in capacitor may be used. Inthis case, the aforementioned guidance display can be used. That is,through the guidance display, an electric power supply status (theremaining battery level) in one or more first radiographic apparatus 10Amay be displayed, e.g., on the display unit 1010 of the console 1004 asa guidance. If each type of the batteries 308 of the one or more firstradiographic apparatus 10A is also displayed in the guidance display, itwill be possible to easily select the most suitable first radiographicapparatus 10A that satisfies the present image capturing conditions(such as the need for the large number of radiographic images to becaptured, or the need for quick radiographic image capturing of a singleimage), based on the electric power supply status of each of the firstradiographic apparatus 10A and each type of the batteries 308.

If the cart unit 1002 is moved by electric power, it is only necessaryto prepare a battery for supplying electric power to an electromotivedrive system of the cart unit 1002. In this case, it is not necessary tosupply electric power to the first radiographic apparatus 10A or otherdevices, but it is sufficient to secure electric power only for themovement of the cart unit 1002. Thus, it is not necessary to useconventional dedicated batteries (lead battery or the like), but it issufficient to use a small lithium battery or the like.

Thus, even if the cart unit 1002 is moved by electric power, the weightof the first mobile apparatus 1000A can be reduced and the first mobileapparatus 1000A is used easily. The battery thereof can be replaced atany place such as a medical site, which can lead to elimination of theneed of charging facilities for a mobile radiographic image capturingapparatus. Then, it becomes unnecessary for the first mobile apparatus1000A to secure electric power to return to the charging facilities, andthe electric power can be sufficiently used for capturing radiographicimages. Also, the first mobile apparatus 1000A can quickly attend tounexpected recapturing or additional capturing of radiographic images.Since the battery can be replaced easily, the first mobile apparatus1000A can be carried to one or more homes in one region for capturingradiographic images of patients receiving home-care services.

In a case where a need arises to capture radiographic images ofexaminees at accident sites, disaster sites, or on transport vehiclessuch as ambulances (while in movement or at rest), railway cars, ships,aircrafts, or the like, the first mobile apparatus 1000A can be moved toan examinee, such as an accident victim or a disaster victim, and canused quickly to start capturing radiographic images of the examinee,without requiring the examinee to be moved unduly to a hospital or thelike. While on a transport vehicle, the first mobile apparatus 1000A canquickly begin capturing radiographic images of the examinee, withouthaving to wait for the transport vehicle to arrive at a station, a port,or an airport. While on an ambulance, the first mobile apparatus 1000Acan send captured radiographic image information to a data center beforethe ambulance reaches the hospital. As a consequence, a doctor at thehospital can recognize the condition of the examinee in advance, andhence can quickly prepare the examinee for treatment.

It is possible to carry one or more first mobile apparatus 1000A on avehicle or the like to perform periodic or temporary medical checkups atschools or large corporations where the number of examinees is large.Usually, since a single mobile medical checkup motor vehicle (of largetype), which is equipped with a single ordinary radiographic imagecapturing apparatus, is dispatched to such locations, it has beencustomary for such examinees to have to wait a very long time beforeradiographic images of the examinees can be captured. According to thepresent invention, one or more first mobile apparatus 1000A housingseveral first radiographic apparatus 10A can be used simultaneously inorder to minimize the waiting time before radiographic images ofexaminees can be captured.

Electric power can be supplied along a wired route or a wireless route.For example, electric power can be supplied along a route from aradiation source device 18 used in an image capturing process to acassette 12 used in the image capturing process, along a route fromanother radiation source device 18, which is not used in an imagecapturing process, to the cassette 12 that is used in the imagecapturing process, or along a route from another cassette 12, which isnot used in an image capturing process, to the cassette 12 that is usedin the image capturing process. In addition, electric power can besupplied along a route from a cassette 12 used in an image capturingprocess to a radiation source device 18 used in the image capturingprocess, or along a route from another radiation source device 18, whichis not used in an image capturing process, to the radiation sourcedevice 18 that is used in the image capturing process. Electric powercan be supplied to a device, e.g., the radiation source device 18 or thecassette 12, in a wireless fashion, when the device enters into an areaenabling wireless supply of electric power thereto.

If an electric power supply route is fixed to a route from the radiationsource device 18 to the cassette 12, or from the cassette 12 to theradiation source device 18, then since a user is required to confirmonly the level of electric power in the supply source, a preparatoryprocess for supplying electric power can be simplified, and radiographicimages can be captured quickly.

If the first energy input/output unit 300 is used via a wired connectionand the second energy input/output unit 302 is used via a wirelessconnection, then composite connections are made available for supplyingelectric power. For example, electric power can be supplied along aroute from the radiation source device 18 to the cassette 12 and anotherradiation source device 18, along a route from the radiation sourcedevice 18 to the cassette 12 and another cassette 12, along a route fromthe cassette 12 to the radiation source device 18 and another cassette12, or along a route from the cassette 12 to the radiation source device18 and another radiation source device 18.

The radiation source device 18 is supplied with electric powerpreferentially from a cassette 12 that has been deteriorated greatly, orfrom a cassette 12 having a small remaining built-in memory capacity.Therefore, electric power stored in a cassette 12, which has not beendeteriorated greatly, or in a cassette 12 having a large remainingbuilt-in memory capacity, can be saved, thereby enabling the firstmobile apparatus 1000A to be readily available for emergencies.

Similarly, the radiation source device 18 is supplied with electricpower preferentially from a cassette 12 that is located closer to theradiation source device 18. Therefore, the time required to supplyelectric power to the radiation source device 18 is shortened, therebymaking the first mobile apparatus 1000A readily available foremergencies.

Similarly, the radiation source device 18 is supplied with electricpower preferentially from a cassette 12 that is smaller in size.Therefore, electric power stored in a cassette 12, which is larger insize and hence more versatile, can be saved, thereby making the firstmobile apparatus 1000A readily available for emergencies.

Since the first mobile apparatus 1000A includes the electric powermanager 390, the level of electric power required to capture a desirednumber of radiographic images is managed, and the remaining levels ofthe batteries 308 in the devices are controlled for flexible electricpower supply. Thus, it is possible to supply electric power from adevice, the battery of which stores excessive electric power to a devicehaving a battery with insufficient electric power, for example, up tothe level of the required electric power. Also, since electric powerrequired to capture radiographic images can flexibly be supplied fromanother device, which is not used in the image capturing process, to adevice which is used in the image capturing process having a batterywith insufficient electric power, for example, up to the level of therequired electric power. As a result, the radiation source device 18 andthe cassette 12 can be supplied efficiently with electric power, therebymaking the first mobile apparatus 1000A readily available in anemergency, and reducing the electric power consumption. Since electricpower can be managed automatically, troublesome procedures such aschecking batteries can be omitted, and image capturing process can beperformed quickly. Further, since the electric power manager 390 isincluded, the printers 170 a, 170 b, 170 c having large electric powerconsumption may be installed in the radiation source device 18 and thecassette 12 of the first radiographic apparatus 10A, and in the firstmobile apparatus 1000A.

The timing at which electric power is supplied can be determined asdesired. For example, the timing at which electric power is supplied canbe determined in order to supply electric energy before an imagecapturing process is carried out. In this manner, electric powerrequired to capture radiographic images can be ensured without wastefulelectric power consumption. Since electric power required to captureradiographic images is predicted and supplied in accordance therewith,electric power is supplied efficiently. If the timing at which electricpower is supplied is determined in order to supply electric energy afteran image capturing process has been performed, then since the amount ofelectric power required to capture at least one radiographic image isensured, the first mobile apparatus 1000A can quickly be readied toperform a next image capturing process.

Supply of electric power is stopped during a period in which noise islikely to be added to radiographic image information being captured.Consequently, wasteful consumption of electric power is minimized forenabling low electric power consumption, while at the same time thequality of the radiographic image information is prevented from becomingdegraded.

In the above embodiment, the battery controller 306 is provided in eachof the devices. However, among the components that make up the batterycontroller 306, the electric power supply controller 374 and theremaining level detector 376 may be provided in each of the devices,whereas the other components thereof may be provided only in one of aradiation source device 18, a cassette 12, and a console 1004, which areused in an image capturing process. Among the components of the electricpower controller 334, only the electric power manager 390 may beprovided in one of the radiation source device 18, the cassette 12, andthe console 1004, which are used in an image capturing process.

In a case where the first mobile apparatus 1000A is moved, the radiationsource device 18 and the cassette 12 of the first radiographic apparatus10A are housed in the slot 1036 of the first mobile apparatus 1000A, inthe state in which the radiation source device 18 and the cassette 12are integrally joined to each other by the joining mechanism 82. Thus,the radiation source device 18 and the cassette 12 are prevented fromfalling down even in a case where the first mobile apparatus 1000Amoves. Further, since it is unnecessary to hold the radiation sourcedevice 18 and the like by hand while the first mobile apparatus 1000A ismoving, the first mobile apparatus 1000A can be moved easily andsmoothly.

For capturing radiographic images, the first radiographic apparatus 10Ais taken out from the slot 1036 of the first mobile apparatus 1000A.After the radiation source device 18 and the cassette 12 are separatedfrom each other, the radiation source device 18 may be attached to thedistal end 1006 a of the arm unit 1006, and the cassette 12 may bedisposed in confronting relation to the radiation source device 18.Thus, the first mobile apparatus 1000A can simply and quickly be readiedfor capturing radiographic images.

Since the console 1004 can supply electric power to respective devices,it is possible to set a supply route from the console 1004 to aradiation source device 18 that is used to capture radiographic images,as well as a supply route from the console 1004 to a cassette 12 that isused to capture radiographic images. It also is possible to set a supplyroute from the console 1004 as a supply source to the aforesaidradiation source device 18, as well as a supply route from the console1004 as a supply source to the aforesaid cassette 12. Furthermore, it ispossible to set a supply route from the aforesaid radiation sourcedevice 18 via the console 1004 to the aforesaid cassette 12, as well asa supply route from the aforesaid cassette 12 via the console 1004 tothe aforesaid radiation source device 18.

Since electric power can be supplied from the console 1004 to theradiation source device 18 and the cassette 12, or electric power can besupplied between the radiation source device 18 and the cassette 12 viathe console 1004, the console 1004 can perform a centralized electricpower management process for efficiently supplying electric powerbetween the radiation source device 18 and the cassette 12. Inasmuch aselectric power can be collected from one or more radiation sourcedevices 18 and one or more cassettes 12 into the console 1004, theconsole 1004 can perform a battery function that enables efficientelectric power management, so as to avoid power supply problems such assudden power supply interruptions in a case where electric power needsto be supplied to the radiation source device 18 and the cassette 12.

In the first mobile apparatus 1000A, the first radiographic apparatus10A may comprise a water-resistant, hermetically sealed structure,thereby making the entire first radiographic apparatus 10A resistant tocontamination by blood and bacteria. If necessary, the firstradiographic apparatus 10A may be cleaned and sterilized for enablingrepetitive use.

The first radiographic apparatus 10A may perform wireless communicationswith an external device by way of ordinary wireless communications usingradio waves, or by way of optical wireless communications using infraredrays or the like.

In the first embodiment, as shown in FIG. 35, the first radiographicapparatus 10A may be devoid of the tape measure 72. Without the tapemeasure 72, the first radiographic apparatus 10A provides the sameadvantages offered by components thereof other than the tape measure 72.

As described above, major components of the joining mechanism 82 areprovided in the cassette 12. However, the joining mechanism 82 may beprovided in the radiation source device 18. Such a modification offersthe same advantages as those referred to above.

The first radiographic apparatus 10A may be modified as described below.

FIG. 36 shows a first radiographic apparatus 10A according to amodification, in which the unlocking button 34, the hook 64, etc., areprovided in the radiation source device 18.

As shown in FIG. 36, the side 14 a of the cassette 12 does not includethe aforementioned holders 16 a, 16 b, and the radiation source device18 has a flat side, which faces the side 14 a of the cassette 12.Opposite ends of the radiation source device 18 have respectiveunlocking buttons 34. The radiation source device 18 also has throughholes 62 and hooks 64 provided in the flat side thereof, which faces theside 14 a of the cassette 12, near opposite ends of the radiation sourcedevice 18. Connection terminals 68 a, 68 b are disposed on the flat sideof the radiation source device 18 near one of the ends of the radiationsource device 18.

The side 14 a of the cassette 12 has through holes 66 defined therein,which are in alignment with the respective through holes 62 andconnection terminals 70 a, 70 b, which in turn are in alignment with theconnection terminals 68 a, 68 b.

The first radiographic apparatus 10A shown in FIG. 36 operates in thefollowing manner. While the flat side of the radiation source device 18and the side 14 a of the cassette 12 face toward each other, the hooks64 are inserted into the respective through holes 66, and the connectionterminals 68 a, 68 b and the connection terminals 70 a, 70 b are broughtinto engagement with each other. In this case, the radiation sourcedevice 18 and the cassette 12 are integrally joined to each other.

The first radiographic apparatus 10A shown in FIG. 36 offers the sameadvantages as the first radiographic apparatus 10A according to thefirst embodiment.

According to the modification shown in FIG. 36, since the unlockingbuttons 34 are disposed on opposite ends of the radiation source device18, an operator 38 can easily disconnect the radiation source device 18from the cassette 12, simply by detaching the radiation source device 18from the cassette 12 while pressing the unlocking buttons 34.

In the first embodiment, as shown in FIG. 37, a cradle 220 for chargingthe batteries 308 of the first radiographic apparatus 10A may bepositioned at a desired location in the hospital, for example. Thecradle 220 is not only capable of charging the batteries 308, but mayalso have a wireless or wired communication function for sending andreceiving necessary information to and from an external device in thehospital, for example. Information sent from the cradle 220 may includeradiation image information recorded in the first radiographic apparatus10A, which is connected to the cradle 220.

The cradle 220 has a display unit 222 for displaying the charged stateof the first radiographic apparatus 10A, which is connected to thecradle 220, and other necessary information, including radiation imageinformation acquired from the first radiographic apparatus 10A.

A plurality of cradles 220 may be connected through a network, andcharged states of respective first radiographic apparatus 10A, which areconnected to the cradles 220, may be retrieved through the network, sothat the user can confirm the locations of first radiographic apparatus10A that are sufficiently charged, based on the retrieved chargedstates.

A mobile radiographic image capturing apparatus according to a secondembodiment of the present invention, which will hereinafter be referredto as a “second mobile apparatus 1000B”, will be described below withreference to FIGS. 38 through 46.

The second mobile apparatus 1000B essentially is identical in structureto the first mobile apparatus 1000A according to the first embodiment,as shown in FIG. 38, but differs therefrom in that one or more mobilesecond radiographic apparatus 10B, which will be described later, areaccommodated in a cart unit 1002.

As shown in FIG. 39, the second radiographic apparatus 10B essentiallyis identical in structure to the first radiographic apparatus 10Aaccording to the first embodiment, but differs therefrom in that adetecting screen 250 is drawn out slightly from the cassette 12 throughthe side 14 b thereof that is remote from the side 14 a on which theholders 16 a, 16 b project, and a weight bar 252 is coupled to a distalend of the detecting screen 250. Among the other sides 14 c, 14 d of thecassette 12, side 14 c has the first energy input/output unit 300 or thesecond energy input/output unit 302 (see FIG. 19) for inputting andoutputting electric power through a wired or wireless link, for example,a USB terminal 28 that serves as an interface means for sending andreceiving information to and from an external device, a card slot 32 forinserting the memory card 30 therein, and the unlocking button 34, to bedescribed later. On an upper surface 254 of the cassette 12, the mobileterminal 42 is mounted, which is detachable from the cassette 12 andincludes the display unit 36 and the operating unit 40, which isoperated by the operator 38. The radiation source device 18 has anexposure switch 48 (see FIG. 13), which can be operated by the operator38 in order to cause the radiation source 44, which shall be descriedlater, to start emitting radiation 46.

The second mobile apparatus 1000B is also carried (moved) to an accidentor disaster site, as well as a patient room in the hospital or a home ofa person receiving home-care services. Thus, in the cassette 12 and theradiation source device 18 of the second radiographic apparatus 10B, atleast a portion surrounding an electric system thereof is often sealed.Therefore, contactless electric power supply through wirelessconnections or the like is desirable for an electric power supplymethod, compared to contact electric power supply by wired connectionsor the like.

FIGS. 39 and 40 show the second radiographic apparatus 10B in a state inwhich the operator 38 has taken out the second radiographic apparatus10B from the slot 1036 of the cart unit 1002. In this state, theradiation source device 18 and the cassette 12 are joined integrally toeach other.

The mobile second radiographic apparatus 10B will be explained in detailwith reference to FIGS. 39 through 46.

As shown in FIG. 45, the upper surface 254 of the cassette 12 has therecess 54, which accommodates the mobile terminal 42 therein. As shownin FIGS. 41 and 42, the cassette 12 houses therein a storage box 256,accommodating therein a roll screen, which constitutes a rolled form ofthe detecting screen 250 and is made of a flexible material permeable toradiation 46. The storage box 256 supports on a side thereof a rotaryencoder 258 for detecting the length by which the detecting screen 250has been reeled out from the storage box 256. The side wall 52 b of thecassette 12, which makes up the side 14 b, has a slot 260 definedtherein, through which the detecting screen 250 can be reeled out fromthe storage box 256.

In a case where the operator 38 pulls the weight bar 252 in a directionaway from the cassette 12, the detecting screen 250 is drawn or extendedout from the storage box 256 through the slot 260. In a case where thesecond radiographic apparatus 10B is being carried, the detecting screen250 is rolled up inside the storage box 256. In a case where the secondradiographic apparatus 10B is operated to capture radiographic images,as shown in FIGS. 44, 45 and 46, the detecting screen 250 is drawn outor extended substantially flatwise underneath the radiation sourcedevice 18 by the operator 38 pulling the weight bar 252. The detectingscreen 250 has gradations 262 on both side edges thereof along thedirection in which the detecting screen 250 is pulled.

As shown in FIG. 44, the detecting screen 250 houses therein a grid 84for removing scattered rays of radiation 46 from the subject 50 in acase where the radiation source 44 applies radiation 46 to the subject50, a radiation detector 86 for detecting radiation 46 that has passedthrough the subject 50, and a lead sheet 89 for absorbing back scatteredrays of radiation 46, which are successively arranged in this order fromthe irradiated surface 20 of the detecting screen 250, i.e., the uppersurface of the detecting screen 250, as shown in FIGS. 43 through 46.The irradiated surface 20 may be constructed as the grid 84. The grid84, the radiation detector 86, and the lead sheet 89 are flexible.

For irradiating the subject 50 with radiation 46 in order to captureradiographic images of the subject 50, a preparatory procedure mustfirst be performed for readying the second radiographic apparatus 10Bfor capturing radiographic images. Such a preparatory procedure includesa process for presetting a source-to-image distance (SID), whichrepresents an distance (imaging distance) between the focus point 122 ofthe radiation source 44 and a position 124 (see FIG. 44) on theradiation detector 86 that lies straight below the focus point 122, anda process for bringing the central position 126 of the irradiatedsurface 20 of the detecting screen 250 into alignment with the center ofa range within which the irradiated surface 20 is irradiated withradiation 46.

The preparatory procedure is carried out as follows. As shown in FIGS.43 through 45, while the radiation source device 18 is separated fromthe cassette 12, the operator 38 pulls the ribbon 76 from the tapemeasure 72 until the length of the ribbon 76, which is reeled out fromthe tape measure 72, becomes equal to the reeled-out length 11 dependingon the SID. The laser pointer 104 is controlled by the radiation sourcecontroller 102 in order to apply a laser beam 128 to the irradiatedsurface 20, thereby displaying a crisscross mark 130 on the irradiatedsurface 20, which represents the center of a range within which theirradiated surface 20 is irradiated with radiation 46.

The operator 38 determines the central position 126 of the irradiatedsurface 20 by observing the gradations 262 thereon. The SID, thereeled-out length 11 depending on the SID, and a distance 12 between theposition 124 or the central position 126 and the side 14 a having thehole 80 through which the ribbon 76 is pulled out, are related to eachother according to the equation SID≈(11²−12²)^(1/2).

After the ribbon 76 has been pulled from the tape measure 72 by thereeled-out length 11, the operator 38 adjusts the position of theradiation source device 18 so as to bring the mark 130 displayed on theirradiated surface 20 into alignment with the central position 126.Thereafter, the operator 38 turns on the exposure switch 48 in order toenable the radiation source 44 to apply radiation 46 with respect to thesubject 50 on the irradiated surface 20, thereby capturing radiographicimages of the subject 50, as shown in FIG. 46. In FIG. 46, an example isshown in which a radiographic image of a hand of the subject 50 iscaptured.

The second mobile apparatus 1000B also operates according to theoperation sequences shown in FIGS. 26 through 32. The second mobileapparatus 1000B is operated according to a preparatory procedure and animage capturing process as follows.

First, the operator 38 performs operations to ready the secondradiographic apparatus 10B for capturing radiographic images at a sitewhere the second mobile apparatus 1000B has been carried. The operator38 operates the operating unit 40 of the mobile terminal 42 (or theoperating unit 1008 of the console 1004) in order to register imagecapturing conditions, including subject information (e.g., SID) of thesubject 50 to be imaged. The operator 38 pulls the weight bar 252 inorder to draw or extend the detecting screen 250 from the storage box256 by a given length (drawn-out length 13), which is required tocapture radiographic images of a region of the subject 50 to be imaged.The rotary encoder 258 detects the drawn-out length 13 of the detectingscreen 250, and sends a signal representative of the detected drawn-outlength 13 to the SID determining unit 168.

If the unlocking button 34 is pressed by the operator 38, the hook 64and the slide 56 are displaced against the resiliency of the spring 60and along the side wall 52 a toward the side wall 52 d, thereby bringingthe hook 64 out of engagement with the edge of the through hole 66.

While the hook 64 is kept out of engagement with the edge of the throughhole 66, i.e., while the operator 38 presses the unlocking button 34,the operator 38 removes or separates the radiation source device 18 fromthe cassette 12. The connection terminal 68 a becomes disengaged fromthe connection terminal 70 a, and the connection terminal 68 b becomesdisengaged from the connection terminal 70 b, thereby releasing theradiation source device 18 and the cassette 12 from each other. Theradiation source device 18, which is released from the cassette 12, isattached to a distal end 1006 a of an arm unit 1006.

Then, the operator 38 sets the imaging distance and brings the mark 130,which is displayed on the irradiated surface 20, into alignment with thecentral position 126. Thereafter, the operator 38 places and positionsthe subject 50 between the irradiated surface 20 and the radiationsource device 18. The operator 38 moves the radiation source device 18in order to reel out the ribbon 76 from the tape measure 72, until theactual reeled-out length of the ribbon 76 reaches the reeled-out length11 depending on the SID.

After having adjusted the position of the radiation source device 18until the mark 130 and the central position 126 are aligned with eachother, the operator 38 places or positions the subject 50 on theirradiated surface 20, so that the center of a region of the subject 50to be imaged is aligned with the central position 126, i.e., theposition of the mark 130.

After the above positional adjustment has been carried out, theradiation source device 18 is secured to the adjusted position by aholder, not shown, for example.

After the subject 50 is positioned, the operator 38 turns on theexposure switch 48 in order to start capturing radiographic images ofthe subject 50.

The second mobile apparatus 1000B offers the same advantages as thefirst mobile apparatus 1000A.

In a case where the second mobile apparatus 1000B is moved, theradiation source device 18 and the cassette 12 of the secondradiographic apparatus 10B are housed in the slot 1036 of the secondmobile apparatus 1000B, in the state in which the radiation sourcedevice 18 and the cassette 12 are integrally joined to each other by thejoining mechanism 82. Thus, the radiation source device 18 and thecassette 12 are prevented from falling down even in a case where thesecond mobile apparatus 1000B moves. Further, since it is unnecessary tohold the radiation source device 18 and the like by hand while the firstmobile apparatus 1000A is moving, the second mobile apparatus 1000B canbe moved easily and smoothly. For capturing radiographic images, thesecond radiographic apparatus 10B is taken out from the slot 1036 of thesecond mobile apparatus 1000B. After the radiation source device 18 andthe cassette 12 are separated from each other, the radiation sourcedevice 18 may be attached to the distal end 1006 a of the arm unit 1006.Also, after the detecting screen 250 is drawn out or extended from thecassette 12, the detecting screen 250 may be disposed in confrontingrelation to the radiation source device 18. Thus, the second mobileapparatus 1000B can simply and quickly be readied for capturingradiographic images.

The storage box 256, which is disposed in the cassette 12, accommodatestherein the detecting screen 250 in a rolled-up form, so as to beflexible and capable of being extended in sheet form. In a case wherethe second radiographic apparatus 10B is housed in the second mobileapparatus 1000B, the detecting screen 250 is stored in a rolled-up forminside the storage box 256. In a case where the second radiographicapparatus 10B is operated to capture radiographic images, the detectingscreen 250 is drawn out from the storage box 256 in a flat sheet form.Therefore, each of the second radiographic apparatus 10B and the secondmobile apparatus 1000B is small in overall size.

For example, if the number of the first radiographic apparatus 10Aaccommodated in the first mobile apparatus 1000A is equal to the numberof the second radiographic apparatus 10B accommodated in the secondmobile apparatus 1000B, the size of the second mobile apparatus 1000Bcan be smaller than the size of the first mobile apparatus 1000A. Also,if the size of the first mobile apparatus 1000A is equal to the size ofthe second mobile apparatus 1000B, the number of the second radiographicapparatus 10B accommodated in the second mobile apparatus 1000B can begreater than the number of the first radiographic apparatus 10Aaccommodated in the first mobile apparatus 1000A.

In the first mobile apparatus 1000A, it may be possible to use both ofthe first radiographic apparatus 10A and the second radiographicapparatus 10B. Also, in the second mobile apparatus 1000B, it may bepossible to use both of the second radiographic apparatus 10B and thefirst radiographic apparatus 10A.

A mobile radiographic image capturing apparatus according to a thirdembodiment of the present invention, which hereinafter will be referredto as a “third mobile apparatus 1000C,” will be described below withreference to FIGS. 47 through 49.

The third mobile apparatus 1000C essentially is identical in structureto the first mobile apparatus 1000A according to the first embodiment,but differs therefrom in that a cart unit 1002 comprises a firstaccommodating unit 1050 for accommodating a radiation source device 18,a second accommodating unit 1052 for accommodating cassettes 12, and animage reading apparatus 1054.

The cassette 12 used in the third mobile apparatus 1000C accommodatestherein a stimulable phosphor panel 500 (see FIG. 49), which storesradiation energy representative of a radiographic image in a phosphor.In a case where the stimulable phosphor panel 500 is irradiated withstimulating light, the phosphor emits stimulated light representing thestored radiographic image. The radiation source device 18 of the firstradiographic apparatus 10A or the second radiographic apparatus 10B isused in the third mobile apparatus 1000C. FIG. 47 shows that the thirdmobile apparatus 1000C accommodates the three cassettes 12 and the threeradiation source device 18, for example.

As shown in FIG. 48, the image reading apparatus 1054 comprises a reader502 for irradiating the stimulable phosphor panel 500 (see FIG. 49) withstimulating light and reading radiation energy representative ofradiographic image information that is stored in the stimulable phosphorpanel 500 (see FIG. 49) by radiography, an image memory 504 for storingthe radiographic image information read by the reader 502, an imageprocessor 506 for performing an image processing process (including acorrecting process) of the radiographic image information stored in theimage memory 504, an ID memory 508 for storing the ID of the readingapparatus for identifying the image reading apparatus 1054, an interface510 (I/F), a transceiver 512 for sending information to and receivinginformation from an external device (a network, a radiation sourcedevice 18, or the like).

The first energy input/output unit 300 or the second energy input/outputunit 302 is mounted, for example, on a side wall of the image readingapparatus 1054. The first energy input/output unit 300 of the imagereading apparatus 1054 may be connected to the first energy input/outputunits 300 of the radiation source devices 18 through wired connections,while the second energy input/output unit 302 of the image readingapparatus 1054 may be connected to the first energy input/output units300 of the radiation source devices 18 through wireless connections.

As shown in FIG. 48, the image reading apparatus 1054 also incorporatestherein a battery unit 304 and a battery controller 306 that are similarto those of the radiation source device 18 and the cassette 12. Thethird mobile apparatus 1000C is also carried (moved) to an accident ordisaster site, as well as a patient room in the hospital or a home of aperson receiving home-care services. Thus, in the radiation sourcedevice 18 and the image reading apparatus 1054, at least a portionsurrounding an electric system thereof is often sealed. Therefore,contactless electric power supply through wireless connections or thelike is desirable for an electric power supply method, compared tocontact electric power supply by wired connections or the like.

As shown in FIG. 49, the image reading apparatus 1054 includes acassette loader 522 disposed in an upper portion of a casing 520. Thecassette loader 522 has a loading slot 524 for receiving the cassette12, which houses therein the stimulable phosphor panel 500 with recordedradiographic image information. Near the loading slot 524, the casing520 accommodates therein a bar-code reader 526 for readingidentification information recorded in a bar code on the cassette 12, anunlocking mechanism 530 for unlocking a lid 528 of the cassette 12, asuction cup 532 for attracting and removing the stimulable phosphorpanel 500 from the cassette 12 in a case where the lid 528 is opened,and a pair of nip rollers 534 for gripping and feeding the stimulablephosphor panel 500 removed by the suction cup 532.

The nip rollers 534 are followed by a plurality of feed rollers 536 athrough 536 g and a plurality of guide plates 538 a through 538 f, whichjointly make up a curved feed path 540. The curved feed path 540 extendsdownwardly from the cassette loader 522, extends substantiallyhorizontally at a lowermost portion thereof, and then extendssubstantially vertically upward. A curved feed path 540 of this shape iseffective in making the image reading apparatus 1054 small in size.

An erasing unit 542 is disposed between the nip rollers 534 and the feedrollers 536 a, for erasing radiographic image information remaining inthe stimulable phosphor panel 500, from which desired radiographic imageinformation has already been read. The erasing unit 542 has a pluralityof erasing light sources 544 such as cold cathode-ray tubes or the likefor emitting erasing light.

A platen roller 546 is disposed between the feed rollers 536 d, 536 e,which are positioned in the lowermost portion of the curved feed path540. The platen roller 546 is disposed beneath a scanning unit 548 forreading desired radiographic image information recorded in thestimulable phosphor panel 500.

The scanning unit 548 comprises a stimulator 550 for emitting a laserbeam LB as stimulating light to scan the stimulable phosphor panel 500,and a reader 502 for reading stimulated light emitted from thestimulable phosphor panel 500, which is stimulated by the laser beam LB.

A stimulator 550 comprises a laser oscillator 552 that outputs the laserbeam LB, a rotary polygon mirror 554 for deflecting the laser beam LB ina main scanning direction across the stimulable phosphor panel 500, anda reflecting mirror 556 for reflecting the laser beam LB toward thestimulable phosphor panel 500 as the stimulable phosphor panel 500passes over the platen roller 546.

The reader 502 comprises a light guide 558 having a lower end disposednear the stimulable phosphor panel 500 over the platen roller 546, and aphotomultiplier 560 connected to an upper end of the light guide 558,for converting stimulated light from the stimulable phosphor panel 500into an electric signal, which represents the radiographic imageinformation stored in the stimulable phosphor panel 500. A lightcollecting mirror 562 for effectively collecting stimulated light fromthe stimulable phosphor panel 500 is disposed near the lower end of thelight guide 558. The radiographic image information read by thephotomultiplier 560 is processed in the image processor 506 (including acorrecting process) in the image reading apparatus 1054. As shown inFIG. 48, the radiographic image information from the reader 502 isstored in the image memory 504, processed in the image processor 506,and sent to the console 1004 or the data center via the transceiver 512,together with the identification information of the image readingapparatus 1054.

In a case where the radiographic image capturing is performed by thethird mobile apparatus 1000C, the radiation source device 18 is takenout from the first accommodating unit 1050 and attached to the distalend 1006 a of the arm unit 1006. The cassette 12 is disposed inconfronting relation to the radiation source device 18, while thesubject 50 is interposed therebetween and the irradiated surface 20faces the radiation source device 18. Then, an image capturing switch isoperated for capturing radiographic images.

After the radiographic images are captured, the cassette 12 is insertedinto the image reading apparatus 1054. The radiographic imageinformation stored in the stimulable phosphor panel 500 in the cassette12 is read and stored in the image memory 504 (see FIG. 48). In thiscase, also, the radiographic image information is sent to the console1004 or the data center via the transceiver 512.

The third mobile apparatus 1000C is controlled so as to supply electricpower from the radiation source device 18 to the image reading apparatus1054, or from the image reading apparatus 1054 to the radiation sourcedevice 18. In other words, the operation of the third mobile apparatus1000C can be explained in the same manner as that of the first mobileapparatus 1000A or the second mobile apparatus 1000B, if the imagereading apparatus 1054 serves as the source and destination of electricpower. Thus, the electric power controller 334 of the third mobileapparatus 1000C basically has a configuration similar to theconfiguration shown in FIG. 21 (first specific example) or shown in FIG.22 (second specific example), and operation sequences similar to thesequences shown in FIGS. 26 through 32. The third mobile apparatus1000C, however, does not incorporate therein the functional componentsrelating to the cassette 12, i.e., any of a cassette selector activator362, a cassette selector 364, an integrated supply activator 366, and anintegrated supply 368. Thus, in the operation sequence shown in FIG. 26,steps S3 and S4 (which relate to the selection of a cassette) and stepsS5 and S6 (which relate to integrated supply) are not performed.

In the third mobile apparatus 1000C as well, since the console 1004 cansupply electric power to respective devices, it is possible to set asupply route from the console 1004 to a radiation source device 18 thatis used to capture radiographic images, as well as a supply route fromthe console 1004 to an image reading apparatus 1054. It also is possibleto set a supply route from the console 1004 as a supply source to theaforesaid radiation source device 18, as well as a supply route from theconsole 1004 as a supply source to the aforesaid image reading apparatus1054. Furthermore, it is possible to set a supply route from theaforesaid radiation source device 18 via the console 1004 to theaforesaid image reading apparatus 1054, as well as a supply route fromthe aforesaid image reading apparatus 1054 via the console 1004 to theaforesaid radiation source device 18.

Since electric power can be supplied from the console 1004 to theradiation source device 18 and the image reading apparatus 1054, orelectric power can be supplied between the radiation source device 18and the image reading apparatus 1054 via the console 1004, the console1004 can perform a centralized electric power management process forefficiently supplying electric power between the radiation source device18 and the image reading apparatus 1054. Inasmuch as electric power canbe collected from one or more radiation source devices 18 and the imagereading apparatus 1054 into the console 1004, the console 1004 canperform a battery function that enables efficient electric powermanagement, so as to avoid power supply problems such as sudden powersupply interruptions in a case where electric power needs to be suppliedto the radiation source device 18 and the image reading apparatus 1054.

Since the cassette 12 itself does not have a memory 330, the associationbetween the radiation source device 18 and the cassette 12, which havebeen used for capturing radiographic images, is provided, e.g., usingthe console 1004. For example, a bar code (ID information) attached tothe cassette 12 is read by the bar-code reader 526, and the console 1004may associate the read ID information of the cassette 12 with the IDinformation from the radiation source device 18.

Since the third mobile apparatus 1000C limits a route for supply ofelectric power, e.g., only the route from the radiation source device 18to the image reading apparatus 1054, or only the route from the imagereading apparatus 1054 to the radiation source device 18. Thus, electricpower does not have to be supplied in vain and the third mobileapparatus 1000C can reduce consumption of electric power. Also, thethird mobile apparatus 1000C offers the same advantages as the firstmobile apparatus 1000A and the second mobile apparatus 1000B.

Although certain preferred embodiments of the present invention havebeen shown and described in detail, it should be understood that variouschanges and modifications may be made to the embodiments withoutdeparting from the scope of the invention as set forth in the appendedclaims.

For example, the radiation detector 86 may be a radiation detector 600according to a modified example shown in FIGS. 50 and 51. FIG. 50 is across-sectional view schematically illustrating the structure of threepixel units of the radiation detector 600 according to a modifiedexample of the invention.

As shown in FIG. 50, the radiation detector 600 includes a signal outputunit 604, a sensor unit 606 (photoelectric converter), and ascintillator 608 that are sequentially laminated on an insulatingsubstrate 602. The signal output unit 604 and the sensor unit 606 form apixel unit. Plural pixel units are arranged in a matrix on the substrate602, such as an array of pixel units arranged in rows and columns. Ineach pixel unit, the signal output unit 604 and the sensor unit 606 arearranged so as to overlap each other.

The scintillator 608 is formed on the sensor unit 606 with a transparentinsulating film 610 interposed therebetween, and has a phosphor filmthat converts radiation 46 incident from the upper side (the sideopposite to the substrate 602) into light and emits the light. It ispreferable that the wavelength range of light emitted by thescintillator 608 be a visible light range (wavelength of 360 nm to 830nm). It is more preferable that the wavelength range of light include agreen wavelength range in order to capture a monochromatic image usingthe radiation detector 600.

Specifically, in a case in which imaging is performed using X-rays asradiation 46, it is preferable that the phosphor used for thescintillator 608 include cesium iodide (CsI). It is more preferable touse CsI(Tl) (thallium-added cesium iodide) having an emission spectrumof 420 nm to 700 nm during the emission of X-rays. The emission peakwavelength of CsI(Tl) in the visible light range is 565 nm.

The scintillator 608, for example, may be formed on a vapor depositionsubstrate by vapor deposition of a columnar crystal of CsI(Tl). As such,in a case in which the scintillator 608 is formed by vapor deposition,an Al plate is generally used as the vapor deposition substrate in termsof the transmittance of X-rays and manufacturing costs, but the vapordeposition substrate is not limited to the Al plate. In a case in whichGOS is used as the scintillator 608, GOS may be applied onto the surfaceof a TFT active matrix substrate to form the scintillator 608, withoutusing the vapor deposition substrate. Alternatively, after thescintillator 608 is formed by applying GOS to a resin base, thescintillator 608 may be attached to a TFT active matrix substrate. Inthis case, even if the application of GOS failed, the TFT active matrixsubstrate would not be damaged.

The sensor unit 606 includes an upper electrode 612, a lower electrode614, and a photoelectric conversion film 616 provided between the upperand lower electrodes 612, 614.

The upper electrode 612 needs to make light generated by thescintillator 608 incident on the photoelectric conversion film 616.Therefore, it is preferable that the upper electrode 612 be made of aconductive material that is at least transparent with respect to theemission wavelength of the scintillator 608. Specifically, it ispreferable that the upper electrode 612 be made of a transparentconducting oxide (TCO) having high transmittance with respect to visiblelight and a small resistance value. A metal thin film, such as an Authin film, may be used as the upper electrode 612. However, if thetransmittance increases to 90% or more, the resistance value is likelyto increase. Therefore, it is preferable that the upper electrode 612 bemade of TCO. For example, it is preferable that the upper electrode 612be made of ITO, IZO, AZO, FTO, SnO₂, TiO₂, ZnO₂, etc. It is mostpreferable that the upper electrode 612 be made of ITO in terms of asimple process, low resistance, and transparency. One upper electrode612 may be common to all pixel units, or the upper electrode 612 may bedivided for each pixel unit.

The photoelectric conversion film 616 includes an organic photoconductor(OPC) and absorbs light emitted from the scintillator 608 and generatesa charge corresponding to the absorbed light. If the photoelectricconversion film 616 includes an organic photoconductor (an organicphotoelectric conversion material), it has a narrow absorption spectrumin the visible light range and absorbs little electromagnetic wavesother than the light emitted from the scintillator 608. Therefore, it ispossible to effectively reduce noise generated due to the absorption ofradiation 46 by the photoelectric conversion film 616. For example, thephotoelectric conversion film 616 may include amorphous silicon insteadof an organic photoconductor. If the photoelectric conversion film 616includes amorphous silicon, it has a wide absorption spectrum and canabsorb light emitted from the scintillator 608 efficiently.

It is preferable that the absorption peak wavelength of the organicphotoconductor forming the photoelectric conversion film 616 be close tothe emission peak wavelength of the scintillator 608 in order to mosteffectively absorb light emitted from the scintillator 608. It is idealthat the absorption peak wavelength of the organic photoconductor isequal to the emission peak wavelength of the scintillator 608. However,if the difference between the absorption peak wavelength and theemission peak wavelength is small, it is possible to sufficiently absorblight emitted from the scintillator 608. Specifically, the differencebetween the absorption peak wavelength of the organic photoconductor andthe emission peak wavelength of the scintillator 608 with respect to theradiation 46 is preferably equal to or less than 10 nm and morepreferably, equal to or less than 5 nm.

Examples of the organic photoconductor capable of satisfying theabove-mentioned conditions include a quinacridone-based organic compoundand a phthalocyanine-based organic compound. For example, the absorptionpeak wavelength of quinacridone in the visible light range is 560 nm.Therefore, if quinacridone is used as the organic photoconductor andCsI(Tl) is used as the material forming the scintillator 608, it ispossible to reduce the difference between the peak wavelengths to 5 nmor less and substantially maximize the amount of charge generated by thephotoelectric conversion film 616.

The sensor unit 606 includes an organic layer that is formed bylaminating or mixing, for example, an electromagnetic wave absorptionportion, a photoelectric conversion portion, an electron transportportion, a hole transport portion, an electron blocking portion, a holeblocking portion, a crystallization prevention portion, an electrode,and an interlayer contact improvement portion. It is preferable that theorganic layer include an organic p-type compound (organic p-typesemiconductor) or an organic n-type compound (organic n-typesemiconductor).

The organic p-type semiconductor is a donor-type organic semiconductor(compound) whose representative example is a hole-transport-type organiccompound and means an organic compound which readily donates electrons.Specifically, in a case in which two organic materials are in contactwith each other during use, one organic compound with low ionizationpotential is the organic p-type semiconductor. Therefore, any organiccompound may be used as the donor-type organic compound as long as ithas an electron donating property.

The organic n-type semiconductor is an acceptor-type organicsemiconductor (compound) whose representative example is anelectron-transport-type organic compound and means an organic compoundwhich readily accepts electrons. Specifically, in a case in which twoorganic compounds are in contact with each other during use, one organiccompound with high electron affinity is the organic n-typesemiconductor. Therefore, any organic compound may be used as theacceptor-type organic compound as long as it has an electron acceptingproperty.

Materials applicable to the organic p-type semiconductor and the organicn-type semiconductor and the structure of the photoelectric conversionfilm 616 have been described in detail in Japanese Laid-Open PatentPublication No. 2009-032854 and thus a detailed description thereof willbe omitted. The photoelectric conversion film 616 may include fullereneor carbon nanotubes.

It is preferable that the thickness of the photoelectric conversion film616 be as large as possible in terms of the absorption of light from thescintillator 608. However, if the thickness of the photoelectricconversion film 616 is greater than a predetermined value, the intensityof the electric field of the photoelectric conversion film 616 generatedby the bias voltage applied from both ends of the photoelectricconversion film 616 is reduced, which makes it difficult to collectcharge. Therefore, the thickness of the photoelectric conversion film616 is preferably from 30 nm to 300 nm, more preferably from 50 nm to250 nm, and most preferably from 80 nm to 200 nm.

One photoelectric conversion film 616 is common to all pixel units.However, the photoelectric conversion film 616 may be divided for eachpixel unit. The lower electrode 614 is a thin film that is divided foreach pixel unit. However, one lower electrode 614 may be common to allpixel units. The lower electrode 614 may be appropriately made of atransparent or opaque conductive material, such as aluminum or silver.The thickness of the lower electrode 614 may be, for example, from 30 nmto 300 nm.

In the sensor unit 606, a predetermined bias voltage can be appliedbetween the upper electrode 612 and the lower electrode 614 to move oneof the charges (a hole and an electron) generated from the photoelectricconversion film 616 to the upper electrode 612 and move the other chargeto the lower electrode 614. In the radiation detector 600 according tothis modified example, a wiring line is connected to the upper electrode612 and the bias voltage is applied to the upper electrode 612 throughthe wiring line. It is assumed that the polarity of the bias voltage isdetermined such that the electron generated in the photoelectricconversion film 616 is moved to the upper electrode 612 and the hole ismoved to the lower electrode 614. However, the polarity may be reversed.

The sensor unit 606 forming each pixel unit may include at least thelower electrode 614, the photoelectric conversion film 616, and theupper electrode 612. In order to prevent an increase in dark current, itis preferable that at least one of electron blocking film 618 and holeblocking film 620 be provided, and it is more preferable that both theelectron blocking film 618 and the hole blocking film 620 be provided.

The electron blocking film 618 may be provided between the lowerelectrode 614 and the photoelectric conversion film 616. In a case inwhich the bias voltage is applied between the lower electrode 614 andthe upper electrode 612, it is possible to prevent an increase in thedark current due to the injection of electrons from the lower electrode614 into the photoelectric conversion film 616.

The electron blocking film 618 may be made of an electron donatingorganic material. In practice, the material used for the electronblocking film 618 may be selected according to a material forming anadjacent electrode and a material forming an adjacent photoelectricconversion film 616. It is preferable that the material used for theelectron blocking film 618 have an electron affinity (Ea) that is atleast 1.3 eV higher than the work function (Wf) of the material formingthe adjacent electrode and have an ionization potential (Ip) equal to orless than that of the material forming the adjacent photoelectricconversion film 616. Materials applicable as the electron donatingorganic material have been described in detail in Japanese Laid-OpenPatent Publication No. 2009-032854 and thus a detailed descriptionthereof will be omitted.

The thickness of the electron blocking film 618 is preferably from 10 nmto 200 nm, more preferably from 30 nm to 150 nm, and most preferablyfrom 50 nm to 100 nm in order to reliably obtain the effect ofpreventing the dark current and prevent a reduction in the photoelectricconversion efficiency of the sensor unit 606.

The hole blocking film 620 may be provided between the photoelectricconversion film 616 and the upper electrode 612. In a case in which thebias voltage is applied between the lower electrode 614 and the upperelectrode 612, it is possible to prevent an increase in the dark currentdue to the injection of holes from the upper electrode 612 into thephotoelectric conversion film 616.

The hole blocking film 620 may be made of an electron accepting organicmaterial. The thickness of the hole blocking film 620 is preferably from10 nm to 200 nm, more preferably from 30 nm to 150 nm, and mostpreferably from 50 nm to 100 nm in order to reliably obtain the effectof preventing the dark current and prevent a reduction in thephotoelectric conversion efficiency of the sensor unit 606.

In practice, the material used for the hole blocking film 620 may beselected according to a material forming an adjacent electrode and amaterial forming an adjacent photoelectric conversion film 616. It ispreferable that the material used for the hole blocking film 620 have anionization potential (Ip) that is at least 1.3 eV higher than the workfunction (Wf) of the material forming the adjacent electrode and have anelectron affinity (Ea) equal to or more than that of the materialforming the adjacent photoelectric conversion film 616. Materialsapplicable as the electron accepting organic material have beendescribed in detail in Japanese Laid-Open Patent Publication No.2009-032854 and thus a detailed description thereof will be omitted.

In a case in which the bias voltage is set such that, among the chargesgenerated in the photoelectric conversion film 616, holes are moved tothe upper electrode 612 and electrons are moved to the lower electrode614, the positions of the electron blocking film 618 and the holeblocking film 620 may be reversed. In addition, it is not necessary toprovide both the electron blocking film 618 and the hole blocking film620. If either the electron blocking film 618 or the hole blocking film620 is provided, it is possible to a certain extent to obtain the effectof preventing the dark current.

As shown in FIG. 51, the signal output unit 604 is provided on thesurface of the substrate 602 so as to correspond to the lower electrode614 of each pixel unit. The signal output unit 604 has a storagecapacitor 622 that stores the charge moved to the lower electrode 614,and a TFT 624 that converts the charge stored in the storage capacitor622 into an electric signal and outputs the electric signal. A region inwhich the storage capacitor 622 and the TFT 624 are formed has a portionthat overlaps the lower electrode 614 in a plan view. In this way, thesignal output unit 604 and the sensor unit 606 in each pixel unitoverlap each other in the thickness direction. It is possible tominimize the plane area of the radiation detector 600 (pixel unit), ifthe signal output unit 604 is formed such that the storage capacitor 622and the TFT 624 are completely covered with the lower electrode 614.

The storage capacitor 622 is electrically connected to the correspondinglower electrode 614 through a conductive line that is formed so as topass through an insulating film 626 provided between the substrate 602and the lower electrode 614. In this way, it is possible to move thecharge captured by the lower electrode 614 to the storage capacitor 622.

The TFT 624 is formed by laminating a gate electrode 628, a gateinsulating film 630, and an active layer (channel layer) 632 andproviding a source electrode 634 and a drain electrode 636 on the activelayer 632 with a predetermined gap therebetween. The active layer 632may be made of, for example, amorphous silicon, an amorphous oxide, anorganic semiconductor material, or carbon nanotubes. The materialforming the active layer 632 is not limited thereto.

An oxide (for example, an In—O-based oxide) including at least one ofIn, Ga, and Zn is preferable as the amorphous oxide that can form theactive layer 632. An oxide (for example, an In—Zn—O-based oxide, anIn—Ga—O-based oxide, or a Ga—Zn—O-based oxide) including at least two ofIn, Ga, and Zn is more preferable as the amorphous oxide. An oxideincluding In, Ga, and Zn is most preferable as the amorphous oxide. Asan In—Ga—Zn—O-based amorphous oxide, an amorphous oxide having acomposition represented by InGaO₃(ZnO)_(m) (m is a natural numbersmaller than 6) in a crystalline state is preferable, and InGaZnO₄ ismore preferable. The amorphous oxide that can form the active layer 632is not limited thereto.

A phthalocyanine compound, pentacene, or vanadyl phthalocyanine may begiven as an example of the organic semiconductor material that can formthe active layer 632, but the organic semiconductor material is notlimited thereto. The structure of the phthalocyanine compound has beendescribed in detail in Japanese Laid-Open Patent Publication No.2009-212389 and thus a detailed description thereof will be omitted.

If the active layer 632 of the TFT 624 is made of an amorphous oxide, anorganic semiconductor material, or carbon nanotubes, radiation 46, suchas X-rays, is not absorbed. Even if the radiation 46 is absorbed, theabsorbed amount will be very small. Therefore, it is possible toeffectively prevent the generation of noise in the signal output unit604.

In a case in which the active layer 632 is made of carbon nanotubes, itis possible to improve the switching speed of the TFT 624 and form theTFT 624 with low light absorptance in the visible light range. Inaddition, in a case in which the active layer 632 is made of carbonnanotubes, even though a very small amount of metallic impurities ismixed with the active layer 632, the performance of the TFT 624 issignificantly reduced. Therefore, it is necessary to separate andextract carbon nanotubes with very high purity using, for example,centrifugal separation and form the active layer 632 with the carbonnanotubes.

All of the amorphous oxide, the organic semiconductor material, thecarbon nanotubes, and the organic photoconductor can be used to form afilm at a low temperature. Thus, the substrate 602 is not limited to asubstrate with high heat resistance, such as a semiconductor substrate,a quartz substrate, or a glass substrate, but a flexible substrate, suchas a plastic substrate, an aramid substrate, or a bio-nanofibersubstrate may be used as the substrate 602. Specifically, for example, aflexible substrate made of the following materials may be used:polyester, such as polyethylene terephthalate, polybutylene phthalate,or polyethylene naphthalate, polystyrene, polycarbonate, polyethersulfone, polyarylate, polyimide, polycycloolefin, norbornene resin, andpolychlorotrifluoroethylene. If such a flexible substrate made ofplastic is used, it is possible to reduce the weight of the substrate.For example, this structure has an advantage in portability.

If the photoelectric conversion film 616 is formed of the organicphotoconductor and the TFT 624 is formed of the organic semiconductormaterial, it is possible to form films of the photoelectric conversionfilm 616 and the TFT 624 at a low temperature with respect to a flexiblesubstrate (substrate 602) of plastic. Also, it is possible to reduce thethickness and weight of the radiation detector 600 in its entirety, andthereby it is possible to reduce the thickness and weight of thecassette 12 housing the radiation detector 600. Accordingly, it ispossible to improve convenience if used outside of a hospital. Further,a base material of the photoelectric conversion unit is made of aflexible material instead of glass that is commonly used. Thus, it ispossible to enhance resistance to damage or the like if the radiographicimage capturing apparatus is carried or used.

In addition, for example, an insulating layer for ensuring an insulatingproperty, a gas barrier layer for preventing the penetration of water oroxygen, and an undercoating layer for improving flatness or the adhesionof, for example, the electrode may be provided on the substrate 602.

Since aramid can be applied to a high-temperature process of 200 degreesor more, a transparent electrode material can be cured at a hightemperature to have low resistance, and the aramid can respond to theautomatic mounting of a driver IC including a solder reflow process. Inaddition, the thermal expansion coefficient of aramid is close to thatof ITO (indium tin oxide) or a glass substrate. Therefore, after anaramid substrate is manufactured, the warping of the aramid substrate issmall and the aramid substrate is less likely to be cracked. Inaddition, aramid is capable of forming a substrate thinner than, forexample, a glass substrate. Aramid may be laminated on a super-thinglass substrate to form the substrate 602.

The bio-nanofiber is a composite of a cellulose microfibril bundle(bacterial cellulose) generated by bacteria (Acetobacter, AcetobacterXylinum) and a transparent resin. The cellulose microfibril bundle has awidth of 50 nm, a size of one-tenth of the visible light wavelength,high strength, high elasticity, and a low thermal expansion coefficient.A transparent resin, such as an acrylic resin or an epoxy resin, isimpregnated into the bacterial cellulose and is then cured to obtainbio-nanofiber that has a light transmittance of about 90% at awavelength of 500 nm while including 60 to 70% of fiber. Thebio-nanofiber has a low thermal expansion coefficient (3 to 7 ppm) equalto that of a silicon crystal, strength (460 MPa) similar to that ofsteel, high elasticity (30 GPa), and flexibility. Therefore, thebio-nanofiber is capable of forming a substrate 602 thinner than, forexample, a glass substrate.

In this example, the signal output unit 604, the sensor unit 606, andthe transparent insulating film 610 are sequentially formed on thesubstrate 602 and the scintillator 608 is bonded to the substrate 602 byan adhesive resin with low light absorptance, thereby forming theradiation detector 600.

In the radiation detector 600 according to the modified example, sincethe photoelectric conversion film 616 is made of an organicphotoconductor and the active layer 632 of the TFT 624 is made of theorganic semiconductor material, radiation 46 is hardly absorbed by thephotoelectric conversion film 616 or the signal output unit 604.Therefore, it is possible to prevent a reduction in sensitivity for theradiation 46.

Both the organic semiconductor material forming the active layer 632 ofthe TFT 624 and the organic photoconductor forming the photoelectricconversion film 616 can be used to form a film at a low temperature.Therefore, the substrate 602 can be made of a plastic resin, aramid, orbio-nanofiber that absorbs a small amount of radiation 46. Accordingly,it is possible to prevent a reduction in sensitivity for the radiation46.

For example, in a case in which the radiation detector 600 is adhered tothe irradiated surface 20 of the housing and the substrate 602 is madeof a plastic resin with high rigidity, aramid, or bio-nanofiber, it ispossible to reduce the thickness of the irradiated surface 20 of thehousing since the radiation detector 600 has high rigidity. In addition,in a case in which the substrate 602 is made of a plastic resin, aramid,or bio-nanofiber having high rigidity, the radiation detector 600 hasflexibility. In a case where the substrate 602 is made of a plasticresin, aramid, or bio-nanofiber having high rigidity, even if an impactis applied to the irradiated surface 20, the radiation detector 600 isless likely to be damaged due to its flexibility.

The radiation detector 600 may be configured as follows.

(1) The photoelectric conversion film 616 may be made of an organicphotoelectric conversion material, for forming a TFT layer 638 usingCMOS sensors. In this case, since only the photoelectric conversion film616 is made of the organic material, the TFT layer 638 including theCMOS sensors does not have to be flexible.

(2) A flexible TFT layer 638 may be formed by the photoelectricconversion film 616 made of an organic photoelectric conversionmaterial, and by CMOS circuits including TFTs 624 made of the organicmaterial. In this case, pentacene may preferably be used as the materialof the organic p-type semiconductor used for the CMOS circuits, andfluorinated copper phthalocyanine (F₁₆CuPc) may preferably be used asthe material of the organic n-type semiconductor. Then, it is possibleto form a flexible TFT layer 638 having a smaller bend radius. With sucha TFT layer 638, it is possible to make the gate insulating film thinnersignificantly, so that the drive voltage can be lower. Further, a gateinsulating film, a semiconductor, each electrode can be made at roomtemperature or at a temperature of 100° C. or lower. Furthermore, CMOScircuits can be fabricated directly on the flexible substrate 602. Also,an organic TFT 624 can be miniaturized using a production processaccording to the scaling law. In forming the substrate 602, if apolyimide precursor is applied to a thin polyimide substrate by a spincoat method and heated, a flat substrate without irregularities can beformed since the polyimide precursor is changed to polyimide.

(3) The Fluidic Self-Assembly technology, which enables a plurality ofmicron-scale device blocks to be assembled in designated positions onthe substrate 602, may be adopted for aligning the photoelectricconversion film 616 of crystal Si and the TFTs 624 on the resinsubstrate 602. In this case, the photoelectric conversion film 616 andthe TFTs 624 as micron-scale device blocks are fabricated on anothersubstrate, and separated from the substrate. In a liquid, thephotoelectric conversion film 616 and the TFTs 624 are suspended andassembled statistically on the target substrate 602. Since the substrate602 is processed beforehand for matching the device blocks, the deviceblocks can be selectively assembled on the target substrate 602.Accordingly, optimum device blocks (photoelectric conversion film 616and TFTs 624) made of optimum material can be integrated on an optimumsubstrate (a semiconductor substrate, a quartz substrate, or a glasssubstrate). Further, optimum device blocks (photoelectric conversionfilm 616 and TFTs 624) can be integrated on a noncrystalline substrate(flexible substrate made of plastics or the like).

The radiation detector 600 according to the modified example is aso-called rear surface reading type (so-called PSS (Penetration SideSampling) type) in which the light emitted from the scintillator 608 isconverted by the sensor unit 606 (photoelectric conversion film 616)into the electric charge for reading the radiographic image, while thesensor unit 606 is positioned on the side opposite to the radiationsource 44. The type of the radiation detector, however, is not limitedthereto.

For example, a radiation detector may be a so-called front surfacereading type (so-called ISS (Irradiation Side Sampling) type). In thiscase, the insulating substrate 602, the signal output unit 604, thesensor unit 606, and the scintillator 608 are successively laminatedalong an irradiation direction of the radiation 46. The light emittedfrom the scintillator 608 is converted by the sensor unit 606 into theelectric charge for reading the radiographic image, while the sensorunit 606 is positioned on the same side as the radiation source 44.Usually, the scintillator 608 emits light having higher intensity on aradiation-irradiated side by the radiation 46 than a back side.Therefore, in the radiation detector of the front surface reading type,the distance from the scintillator 608 to the photoelectric conversionfilm 616, by which emitted light travels, can be shorter than in theradiation detector 600 of the rear surface reading type. Thus, it ispossible to reduce the diffusion or attenuation of the light. As aresult, the resolution of the radiographic image can be higher.

What is claimed is:
 1. A radiographic image capturing apparatuscomprising: a mobile cart unit; a plurality of devices used forcapturing a radiographic image; an electric power supply activatorenabling supply of electric power between the devices, based on aninstruction of permission to supply electric power; an electric powermanager activatable by the electric power supply activator, based on theinstruction of permission to supply electric power, wherein the devicesat least comprise: a radiation source device including a radiationsource for outputting radiation; and a detector device detachablyattached to the cart unit, and including a radiation detector fordetecting radiation that is transmitted through a subject in a casewhere the subject is irradiated with the radiation by the radiationsource, and converting the detected radiation into radiographic imageinformation, and wherein the electric power manager includes anamount-of-consumed-electric-power predictor that calculates and predictsamounts of electric power consumption used to capture radiographicimages by each of the radiation source device and the detector device,the electric power manager, based on the electric power consumptionpredicted by the amount-of-consumed-electric-power predictor, isconfigured to manage electric power required to capture a given numberof radiographic images, and is configured to flexibly supply at leastpart of the required electric power to at least one of the radiationsource device and the detector device, thereby to supply electric powerfrom a device, the battery of which stores excessive electric power to adevice having a battery with insufficient electric power.
 2. Theradiographic image capturing apparatus according to claim 1, wherein theamount-of-consumed-electric-power predictor calculates and predicts,from battery charging conditions and present or previous image capturingconditions, amounts of electric power consumption used to captureradiographic images by each of the radiation source device and thedetector device.
 3. The radiographic image capturing apparatus accordingto claim 1, wherein the amount-of-consumed-electric-power predictorcalculates and predicts, from battery charging conditions, present orprevious image capturing conditions, and usage history, amounts ofelectric power consumption used to capture radiographic images by eachof the radiation source device and the detector device.
 4. Theradiographic image capturing apparatus according to claim 3, wherein theamount-of-consumed-electric-power predictor calculates, from batterycharging conditions and present or previous image capturing conditions,amounts of electric power consumption used to capture radiographicimages by each of the radiation source device and the detector device,and corrects each amount of electric power consumption by multiplyingcoefficients corresponding to the number of times that each of theradiation source device and the detector device has been used.
 5. Amethod for a radiographic image capturing apparatus including: a mobilecart unit, a plurality of devices used for capturing a radiographicimage, and an electric power supply activator enabling supply ofelectric power between the devices, based on an instruction ofpermission to supply electric power, wherein the devices at leastcomprise: a radiation source device including a radiation source foroutputting radiation; and a detector device detachably attached to thecart unit, and including a radiation detector for detecting radiationthat is transmitted through a subject in a case where the subject isirradiated with the radiation by the radiation source, and convertingthe radiographic image information, the method comprising: predictingamounts of electric power consumption used to capture radiographicimages by each of the radiation source device and the detector device,based on an instruction of permission to supply electric power; managingelectric power required to capture a given number of radiographicimages; and supplying at least part of the required electric powerflexibly to at least one of the radiation source device and the detectordevice, thereby to supply electric power from a device, the battery ofwhich stores excessive electric power to a device having a battery withinsufficient electric power.
 6. The method according to claim 5, whereinpredicting the amounts of electric power consumption includescalculating and predicting, from battery charging conditions and presentor previous image capturing conditions, amounts of electric powerconsumption used to capture radiographic images by each of the radiationsource device and the detector device.
 7. The method according to claim5, wherein predicting the amounts of electric power consumption includescalculating and predicting, from battery charging conditions, present orprevious image capturing conditions, and usage history, amounts ofelectric power consumption used to capture radiographic images by eachof the radiation source device and the detector device.
 8. The methodaccording to claim 7, wherein predicting the amounts of electric powerconsumption includes: calculating, from battery charging conditions andpresent or previous image capturing conditions, amounts of electricpower consumption used to capture radiographic images by each of theradiation source device and the detector device, and correcting eachamount of electric power consumption by multiplying coefficientscorresponding to the number of times that each of the radiation sourcedevice and the detector device has been used.